Sinus illumination lightwire device

ABSTRACT

An illuminating wire medical device may include an elongate flexible housing and an illuminating fiber and a core wire extending through at least part of the housing, the core wire providing desired pushability and torquability. The illuminating device may further include a connector assembly cooperating with the illuminating fiber to accommodate changes in length, to absorb forces applied during use of the device and to channel errant light away from the illuminating fibers of the device.

FIELD OF THE INVENTION

The present invention relates generally to medical devices, systems and methods and more particularly to methods and devices for performing minimally invasive procedures that reduce the need to provide fluoroscopic or other radiographic visualization.

BACKGROUND

The skull contains a series of cavities known as paranasal sinuses that are connected by passageways. The paranasal sinuses include frontal sinuses, ethmoid sinuses, sphenoid sinuses and maxillary sinuses. The paranasal sinuses are lined with mucus-producing mucosal tissue and ultimately open into the nasal cavity. Normally, mucus produced by the mucosal tissue slowly drains out of each sinus through an opening known as an ostium. If the mucosal tissue of one of these passageways becomes inflamed for any reason, the cavities which drain through that passageway can become blocked. This blockage can be periodic (resulting in episodes of pain) or chronic. This interference with drainage of mucus (e.g., occlusion of a sinus ostium) can result in mucosal congestion within the paranasal sinuses. Chronic mucosal congestion of the sinuses can cause damage to the epithelium that lines the sinus with subsequent decreased oxygen tension and microbial growth (e.g., a sinus infection).

The term “sinusitis” refers generally to any inflammation or infection of the paranasal sinuses caused by bacteria, viruses, fungi (molds), allergies or combinations thereof. It has been estimated that chronic sinusitis (e.g., lasting more than 3 months or so) results in 18 million to 22 million physician office visits per year in the United States. Patients who suffer from sinusitis typically experience at least some of the following symptoms: headaches or facial pain; nasal congestion or post-nasal drainage; difficulty breathing through one or both nostrils; bad breath; and/or pain in the upper teeth.

One of the ways to treat sinusitis is by restoring the lost mucus flow. The initial therapy is typically drug therapy using anti-inflammatory agents to reduce the inflammation and antibiotics to treat the infection. A large number of patients do not respond to drug therapy. Currently, the gold standard for patients with chronic sinusitis that do not respond to drug therapy is a corrective surgery called Functional Endoscopic Sinus Surgery (FESS).

During FESS, an endoscope is inserted into the nose and, under visualization through the endoscope, the surgeon may remove diseased or hypertrophic tissue or bone and may enlarge the ostia of the sinuses to restore normal drainage of the sinuses. FESS procedures are typically performed with the patient under general anesthesia.

Although FESS continues to be the gold standard therapy for surgical treatment of severe sinus disease, FESS does have several shortcomings. For example, FESS can cause significant post-operative pain. Also, some FESS procedures are associated with significant postoperative bleeding and, as a result, nasal packing is frequently placed in the patient's nose for some period of time following the surgery. Such nasal packing can be uncomfortable and can interfere with normal breathing, eating, drinking etc. Also, some patients remain symptomatic even after multiple FESS surgeries. Additionally, some FESS procedures are associated with risks of iatrogenic orbital, intracranial and sinonasal injury. Many otolaryngologists consider FESS an option only for patients who suffer from severe sinus disease (e.g., those showing significant abnormalities under CT scan). Thus, patients with less severe disease may not be considered candidates for FESS. One of the reasons why FESS procedures can be bloody and painful relates to the fact that instruments having straight, rigid shafts are used. In order to target deep areas of the anatomy with such straight rigid instrumentation, the physician needs to resect and remove or otherwise manipulate any anatomical structures that may lie in the direct path of the instruments, regardless of whether those anatomical structures are part of the pathology.

New devices, systems and techniques are being developed for the treatment of sinusitis and other disorders of the ear, nose, throat and paranasal sinuses. For example, various catheters, guidewires and other devices useable to perform minimally invasive, minimally traumatic ear, nose and throat surgery have been described in U.S. patent application Ser. No. 10/829,917, entitled “Devices, Systems and Methods for Diagnosing and Treating Sinusitis and Other Disorders of the Ears, Nose and/or Throat;” Ser. No. 10/912,578, entitled “Implantable Device and Methods for Delivering Drugs and Other Substances to Treat Sinusitis and Other Disorders;” Ser. No. 10/944,270, entitled “Apparatus and Methods for Dilating and Modifying Ostia of Paranasal Sinuses and Other Intranasal or Paranasal Structures;” Ser. No. 11/037,548, entitled “Devices, Systems and Methods For Treating Disorders of the Ear, Nose and Throat;” and Ser. No. 11/116,118, entitled “Methods and Devices For Performing Procedures Within the Ear, Nose, Throat and Paranasal Sinuses.” Each of these applications is hereby incorporated herein, in its entirety, by reference thereto. Many of these new devices, systems and techniques are useable in conjunction with endoscopic, radiographic and/or electronic assistance to facilitate precise positioning and movement of catheters, guidewires and other devices within the ear, nose, throat and paranasal sinuses and to avoid undesirable trauma or damage to critical anatomical structures such as the eyes, facial nerves and brain.

For example, in one new procedure (referred to in this patent application as a “Flexible Transnasal Sinus Intervention” or FTSI), a dilatation catheter (e.g., a balloon catheter or other type of dilator) is advanced through the nose to a position within the ostium of a paranasal sinus or other location, without requiring removal or surgical alteration of other intranasal anatomical structures. The dilatation catheter is then used to dilate the ostium or other anatomical structures to facilitate natural drainage from the sinus cavity. In some cases, a tubular guide may be initially inserted through the nose and advanced to a position near the sinus ostium and a guidewire may then be advanced through the tubular guide and into the affected paranasal sinus. The dilatation catheter may then be advanced over the guidewire and through the tubular guide to a position where its dilator (e.g., balloon) is positioned within the sinus ostium. The dilator (e.g., balloon) is then expanded causing the ostium to dilate. In some cases, such dilatation of the ostium may fracture, move or remodel bony structures that surround or are adjacent to the ostium. Optionally, in some procedures, irrigation solution and/or therapeutic agents may be infused through a lumen of the dilatation catheter and/or other working devices (e.g., guidewires, catheters, cannula, tubes, dilators, balloons, substance injectors, needles, penetrators, cutters, debriders, microdebriders, hemostatic devices, cautery devices, cryosurgical devices, heaters, coolers, scopes, endoscopes, light guides, phototherapy devices, drills, rasps, saws, etc.) may be advanced through the tubular guide and/or over the guidewire to deliver other therapy to the sinus or adjacent tissues during the same procedure in which the FTSI is carried out. It is to be understood that, in FTSI procedures, structures and passageways other than sinus ostia may be dilated using the tools described above, tissue may be resected or ablated, bone may be restructured, drugs or drug delivery systems may be deployed, etc., as described in the documents incorporated herein by reference. Thus, for the purposes of this application the term FTSI will be generally used to refer broadly to all of those procedures, not just dilation of sinus ostia.

In FTSI procedures that include positioning of a guidewire into a paranasal sinus, the placement of the guidewire is typically confirmed by visualizing the procedure under fluoroscopy or other x-ray visualization technique, for example. Appropriate positioning of the tubular guide at the position near the sinus ostium may also be confirmed via fluoroscopy. Reaching and accessing target anatomy can be a challenge in general and more so in particular patients as anatomy can both be variable and unpredictable. Additionally, the devices employed in a medical procedure must be durable to withstand stresses during normal operating conditions as well as those resulting from unexpected challenges. In order to reduce the radiation exposure to the patient undergoing the procedure, and particularly to the surgeon and other personnel that carry out many of these types of procedures, there is a need for methods and devices that eliminate or reduce the need to use fluoroscopic visualization during such procedures. There is also a need for a medical device that embodies acceptable torquability and pushability. Further, there is a need for a device that has structure which facilitates the accommodation of forces placed thereon. At least some of these objectives will be met by the present invention.

SUMMARY

Briefly and in general terms, the present disclosure is directed towards an apparatus and method for facilitating visualization of target anatomy. In one approach, the apparatus is embodied in an illuminating device configured to be positioned at or adjacent anatomy within a patient's body. The illuminating device can be employed to provide transillumination.

In one aspect, the illuminating device is embodied in an elongate member having proximal and distal portions, where the distal portion is configured to be placed at an interventional site. At the proximal portion of the device is configured a connector. The elongate member can further include an internal bore for receiving substructures of the device.

In one embodiment an illuminating guidewire device comprises:

an elongate flexible housing having a proximal end, a distal end configured to be placed at the site within a patient's body, and a lumen extending through the housing from the proximal end to the distal end, wherein the housing comprises at least a first portion of a first material (e.g., a coil) and a second portion of a second material (e.g., a cable tube) which first and second portions are joined together by a first joint and a second joint;

at least one illuminating fiber extending through the lumen of the housing;

at least one supporting member (e.g., a core wire) extending at least through the lumen of the housing where the first joint and second joint are located and wherein the first joint bonds the first portion of the housing to the supporting member and the second joint bonds the first portion of the housing to the second portion of the housing and the supporting member.

In another embodiment, the invention is directed toward a proximal assembly of an illuminating guidewire comprising:

a first tube (e.g., a hypotube) having a lumen extending therethrough;

an elongate flexible housing (e.g., a cable tube) having a lumen extending therethrough, the housing being received within the first tube but not extending proximally beyond the proximal end of the first tube;

a second tube (e.g., a bonding tube) having a lumen therethrough and positioned within the lumen of the first tube at the proximal end and extending beyond the proximal end of the first tube, but not beyond the distal end of the first tube;

at least one illuminating fiber extending through and proximally beyond the lumen of the housing and the lumen of the first tube and into the lumen of the second tube; and

wherein the housing is not fixably attached to the first tube and is free to rotate within the first tube and the distal end of the second tube and the proximal end of the first tube are fixably attached.

Yet another embodiment relates to a connector adapted to receive an illuminated guidewire having an outer diameter and comprising:

-   -   a proximal portion;     -   a distal portion; and     -   a bore extending through the proximal and distal portions and         having a diameter in the proximal portion (e.g., an aperture)         that is less than the diameter of the outer diameter of the         illuminated guidewire.

In a specific embodiment of an illuminating device, the distal portion includes a coil and the proximal portion includes a cable tube. Extending longitudinally within the proximal and distal portions is one or more illumination fibers, a distal end of which is affixed within the coil and a proximal end. Also configured within certain portions of the proximal and distal portions are a core wire and a stranded wire. Various approaches to receiving the illumination fibers within the connector and profiles of the core wire are contemplated as are points of attachment and relative movements between the components.

Another specific embodiment includes design of the proximal end of the illuminating device which connects to a light source through a detachable connector which receives the illuminated device and then connects to the light cable of the light source and certain features of the detachable connector are contemplated

In a specific embodiment of an illuminating device with an end connector, the distal portion includes a coil and the proximal portion includes a cable tube. Extending longitudinally within the proximal and distal portions is one or more illumination fibers, a distal end of which is affixed within the coil and a proximal end being received within the connector. Also configured within the proximal and distal portions is a core wire. Various approaches to receiving the illumination fibers within the connector and profiles of the core wire are contemplated as are points of attachment and relative movements between the components. Moreover, various embodiments of the connector are contemplated.

Further, approaches to compensating for changing lengths of an illumination fiber are contemplated as are approaches to facilitating the operation of the illuminating device. In that regard, structure can be incorporated into the illuminating device to accommodate changes in length or steps can be taken to treat the illumination fiber to control length changes. Also, drugs can be injected at an interventional site to aid the illumination process.

A method for visually confirming the positioning of a distal end portion of a device placed within a patient is provided to include: inserting a distal end portion of an illuminating device internally into a patient, emitting light from the distal end portion of the illuminating device; observing transillumination resulting from the light emitted from the distal end portion of the illuminating device that occurs on an external surface of the patient; and correlating the location of the observed transillumination on the external surface of the patient with an internal location of the patient that underlies the location of observed transillumination, to confirm positioning of the distal end portion of the illuminating device.

In at least one embodiment, the observation is performed by direct line of sight human observation, without the need for fluoroscopy.

In at least one embodiment, the observation is performed by direct line of sight human observation, without the need for any visualization equipment.

In at least one embodiment, the illuminating device comprises a guidewire.

In at least one embodiment, the illuminating device comprises an ostium seeker device.

In at least one embodiment, the illuminating device comprises a sinus suction instrument.

In at least one embodiment, the illuminating device comprises an integrated wire dilatation catheter, wherein an integrated illuminating guidewire extends distally of a distal end of a dilatation catheter.

In at least one embodiment, the distal end portion of the illuminating guidewire is inserted into a sinus passageway of the patient.

In at least one embodiment, the distal end portion of the illuminating guidewire is inserted through an ostium opening to a sinus of the patient, and the distal end portion is advanced into the sinus.

In at least one embodiment, the distal end portion of the illuminating guidewire is initially inserted through a nostril of the patient and then advanced into a sinus.

In at least one embodiment, a scope is inserted through the nostril of the patient, wherein the guidewire is inserted adjacent the scope, and visualization of the advancement of the distal end portion of the guidewire is performed via the scope as the distal end portion is advanced toward an ostium of the sinus.

In at least one embodiment, transillumination is observed when a light emitting portion of the distal end portion is located in the sinus of the patient.

If observation of transillumination and correlation reveals that the distal end portion of the illumination device has been misrouted to a location other than a target location, the distal end portion of the device can be retracted and re-routed to the target location, which can be confirmed by observing transillumination and correlating.

In observing transillumination, the motion of the transillumination spot resulting from the light emitted from the distal end portion of the illuminating device can be observed and tracked or followed visually, as the distal end portion is moved relative to the patient, and this can be one way of confirming that the transillumination spot in motion correlates to a position of the distal end portion. This technique can be particularly useful when there are additional sources of transillumination, such as a light from a scope, for example.

Further, transillumination resulting from the light emitted from the distal end portion of the device can be distinguished from transillumination resulting from light emitted from a scope by identifying a transillumination spot that is at least one of brighter, smaller or more well-defined than other transillumination effects observed. Alternatively, the transillumination resulting from the light emitted from the distal end portion of the device can be distinguished from transillumination resulting from light emitted from a scope by turning off or down the light source to the scope.

In at least one embodiment, a sinus guide is inserted within the patient prior to inserting the device, and the distal end portion of the illuminating device is inserted through the sinus guide.

In at least one embodiment, the illuminating device is preloaded in the guide, and the guide and preloaded illuminating device are inserted together into the patient. Advancement of the illuminating device relative to the guide can then be performed to extend a distal end portion of the illuminating device distally of a distal end of the guide.

A scope may be inserted within the patient, wherein the sinus guide is inserted adjacent the scope, and advancement of the sinus guide can be visualized via the scope.

In at least one embodiment, visualization of the advancement of the sinus guide is through use of the scope, up to a limit of adequate illumination by the scope. After that, the light emitted by the distal end portion of the illuminating device, having been advanced distally of a distal end of the sinus guide, extends the limit of adequate illumination of the scope, thereby extending a length of the adequate illumination of the scope.

In at least one embodiment, the sinus guide can be further distally advanced under visualization by the scope as facilitated by the extended length of the adequate illumination.

In at least one embodiment, visualization of the advancement of the illuminating device distally of the sinus guide can be performed via the scope, as facilitated by the light emitted from the distal end portion of the device.

In at least one embodiment, the scope is inserted into a nostril of the patient, and the sinus guide is inserted adjacent the scope.

In at least one embodiment, the scope and sinus guide are advanced into a sinus passageway of the patient.

In at least one embodiment, the sinus guide is further advanced toward an ostium of a sinus, and the advancement of the sinus guide is visually observed via the scope.

In at least one embodiment, the scope is inserted into a nostril of the patient, and the sinus guide is inserted adjacent the scope. The advancement of the sinus guide into a sinus passageway is visualized via the scope until a distal end of the sinus guide has reached a distal limit of illumination emitted by the scope.

In at least one embodiment, further advancement of the sinus guide toward an ostium of a sinus is visualized via the scope as facilitated by the extended length of adequate illumination provided by the illumination device.

In at least one embodiment, the scope is inserted into a nostril of the patient, and the sinus guide is inserted adjacent the scope. The advancement of the sinus guide to place a distal end of the sinus guide adjacent an approach to an ostium of a sinus is visualized via the scope.

In at least one embodiment, the distal end portion of the illuminating device is advanced further distally of a distal end of the sinus guide and distal of the limit of illumination of the scope to emit illumination, thereby extending a length of a space that is visualizable by the scope.

In at least one embodiment, the distal end portion of the device is further advanced into and through the ostium, and visualization of the advancement of the distal end portion into the ostium is performed via the scope.

In at least one embodiment the device comprises an illuminating guidewire, a working device is advanced over the guidewire to position a working end of the working device at a target location, and a surgical procedure is performed with the working device at the target location. The working device is removed from the patient after performing the surgical procedure. Optionally, an implant can be left at the target location.

A method of performing a minimally invasive surgical procedure is provided, including the steps of: inserting a distal end portion of an illuminating guidewire internally into a patient; emitting light from the distal end portion of the illuminating guidewire, wherein a proximal end portion is connected to a power source to enable the distal end portion to emit light; observing transillumination resulting from the light emitted from the distal end portion of the illuminating guidewire that occurs on an external surface of the patient; correlating the location of the observed transillumination on the external surface of the patient with an internal location of the patient that underlies the location of observed transillumination, to confirm positioning of the distal end portion of the illuminating guidewire; disconnecting the proximal end portion of the illuminating guidewire from the power source; advancing a working device over the guidewire so that a proximal end of the guidewire extends proximally from the working device; reconnecting the proximal end portion of the illuminating guidewire to the power source so that the distal end portion of the guidewire again emits light; positioning a working end of the working device at a target location; and performing a surgical procedure with the working device at the target location.

After performing the surgical procedure, the proximal end portion of the illuminating guidewire is disconnected from the power source; and the working device is removed from the patient and from the guidewire. Optionally, an implant can be left at the target location.

In at least one embodiment, a second working device is advanced over the guidewire after removing the first working device therefrom, so that a proximal end of the guidewire extends proximally from the second working device. Then the proximal end portion of the illuminating guidewire is reconnected to the power source so that the distal end portion of the guidewire again emits light.

In at least one embodiment, the illuminating guidewire includes at least one illumination fiber extending from a proximal end of the guidewire to the distal end portion, and the power source is a light source.

In at least one embodiment, the illuminating guidewire includes at least one laser fiber extending from a proximal end of the guidewire to the distal end portion, and the power source is a laser light source.

In at least one embodiment, the illuminating guidewire includes a light emitting diode at the distal end portion and electrical wires extending through the guidewire, electrically connecting the light emitting diode to the power source, and wherein the power source is an electrical power source.

A method for diagnosing and/or treating sinusitis or another disorder affecting a nose, a sinus or other anatomical structure of the ear, nose or throat in a human or animal patient is provided, including the steps of: advancing an introducing device through the nose and to a position where the distal end of the introducing device is near an opening of a sinus; advancing a distal end portion of an illuminating device that emits light from the distal end portion thereof through the introducing device while a proximal end of the illuminating device is connected to a power source; and monitoring a position of the distal end portion of the illuminating device distally of the distal end of the introducing device, by observing transillumination on an external surface of the patient that results from the light emitted by the distal end portion. The light emitted can be a desired wavelength in the visible spectrum and/or infrared spectrum.

In at least one embodiment, the distal end portion of the illuminating device is advanced through the opening of the sinus; and placement of the distal end portion of the illuminating device in the sinus is confirmed by observing the transillumination resulting from the light emitted from the distal end portion of the illuminating device that occurs on the external surface of the patient, and correlating the location of the observed transillumination on the external surface of the patient with an internal location of the patient that underlies the location of observed transillumination.

In at least one embodiment, the external surface on which the transillumination is observed is on the face of the patient.

In at least one embodiment, the external surface on which the transillumination is observed is on the palate of the patient.

In at least one embodiment the illuminating device comprises an illuminating guidewire, and a working device is provided that is positionable in an operative location and useable to perform a diagnostic or therapeutic procedure there. The proximal end of the illuminating guidewire is disconnected from the power source, while maintaining the distal end portion of the illuminating guidewire in its current position, and the working device is advanced over the guidewire so that a proximal end of the guidewire extends proximally from the working device. The proximal end of the illuminating guidewire is then reconnected to the power source so that the distal end portion of the guidewire again emits light. The working device is further advanced to position a working end of the working device at the operative location, and a diagnostic or therapeutic procedure is performed with the working device at the operative location.

In at least one embodiment, the operative location is the opening to the sinus.

An illuminating guidewire device is provided, including: a flexible distal end portion; a relatively less flexible proximal end portion; at least one light emitting element in the distal end portion; and at least one structure extending from a proximal end of the device through the proximal end portion and at least part of the distal end portion to connect the at least one light emitting element with a power source located proximally of the device.

In at least one embodiment, the at least one light emitting element comprises a distal end of at least one illumination fiber, and the at least one structure comprises the at least one illumination fiber running proximally of the distal end of the fiber to the proximal end of the device.

In at least one embodiment, the power source is a light source.

In at least one embodiment, the at least one light emitting element of the illuminating guidewire comprises a distal end of at least one laser fiber, and the at least one structure comprises the at least one laser fiber running proximally from the distal end of the fiber to the proximal end of said device.

In at least one embodiment, the power source is a laser light source.

In at least one embodiment, the at least one light emitting element comprises a light emitting diode, and the at least one structure comprises at least one electrical wire electrically connected to the light emitting diode and extending proximally of the light emitting diode to the proximal end of the device.

In at least one embodiment, the power source is an electrical power source.

In at least one embodiment, the distal end portion of the guidewire has an outside diameter configured and dimensioned to pass through an ostium of a sinus.

In at least one embodiment, the distal end portion of the guidewire has an outside diameter less than about 0.038 inches.

In at least one embodiment, the distal end portion of the guidewire has an outside diameter of about 0.035″±0.005″.

In at least one embodiment, the illuminating guidewire has a maximum outside diameter of less than about 0.038 inches.

In at least one embodiment, the illuminating guidewire has a maximum outside diameter of less than about 0.035 inches.

In at least one embodiment, the illuminating guidewire has a maximum outside diameter of about 0.035″±0.005″.

In at least one embodiment, the distal end portion of the device comprises a flexible coil. In at least one embodiment, the distal end portion further comprises a core wire extending internally of the coil. In at least one embodiment, the core wire is fixed to the coil.

In at least one embodiment, a core wire extends within the distal and proximal end portions of the device. In at least one embodiment, core wire extends within substantially the full length of the distal and proximal end portions.

In at least one embodiment, the distal end portion of the device includes a bend, such that a proximal part of the distal end portion is substantially aligned with a longitudinal axis of the device, and a distal part of the distal end portion is angled with respect to the longitudinal axis.

In at least one embodiment, the distal end of at least one illumination fiber is configured to emit light from a distal tip of the distal end portion of the device. The distal tip can be designed to either focus or distribute the light to achieve maximum transillumination. The distal tip can include a lens, prism or diffracting element.

In at least one embodiment, the distal end of at least one illumination fiber is positioned proximally of a distal tip of the distal end portion of the device.

In at least one embodiment, a flexible distal portion of the distal end portion extends distally of the distal end of the at least one illumination fiber.

In at least one embodiment, the distal end of at least one laser fiber is configured to emit light from a distal tip of the distal end portion of the device.

In at least one embodiment, the distal end of at least one laser fiber is positioned proximally of a distal tip of the distal end portion of the device.

In at least one embodiment, a flexible distal portion of the distal end portion extends distally of the distal end of at least one illumination fiber.

In at least one embodiment, a light emitting diode is mounted at a distal tip of the distal end portion of the device.

In at least one embodiment, a light emitting diode is positioned proximally of a distal tip of the distal end portion of the device. In at least one embodiment, a flexible distal portion of the distal end portion extends distally of the light emitting diode.

In at least one embodiment, an electrical power source is removably, electrically connected to at least one structure to provide electrical power to at least one light emitting element.

In at least one embodiment, at least one light conducting tube delivers light from a proximal end portion of the device to a distal end of the tube, where it is emitted.

In at least one embodiment, each light conducting tube is sealed in a proximal end of the device.

In at least one embodiment, each light emitting element is sealed at a distal tip of the device.

In at least one embodiment, a quick release connector is mounted over at least part of the proximal end portion of the guidewire. The quick release connector is adapted to be connected to a power source and to quickly connect to and release from the proximal end portion of the guidewire.

In at least one embodiment, the quick release connector is optically coupled with a light source.

In at least one embodiment, the proximal end portion of the quick release connector is adapted to connect with a light source.

In at least one embodiment, the proximal end portion of the quick release connector comprises an ACMI Corporation light post.

In at least one embodiment, the connector is rotatable with respect to a light channel extending from a light source, when the connector is connected to the light channel. In at least one embodiment, the light cable comprises a fluid filled light cable.

In at least one embodiment, a distal end portion of the connector comprises an opening configured to slidably receive the proximal end portion of the guidewire device; and a quick release locking mechanism is configured to fix the proximal end portion received in the connector.

In at least one embodiment, the quick release locking mechanism is movable between an unlocked configuration in which the proximal end portion can be slid from the connector to disconnect therefrom, and a locked configuration that maintains the proximal end portion in connection with the connector. In at least one embodiment, the quick release locking mechanism is biased toward the locked configuration.

In at least one embodiment, a radiopaque marker is provided on the distal end portion of the guidewire.

In at least one embodiment, an electromagnetic coil is provided at the distal end portion of the guidewire. Alternatively, a magnet, radiofrequency emitter or ultrasound crystal can be provided at the distal end portion of the guidewire.

An illuminating device is provided, including a distal end portion having an outside diameter configured and dimensioned to pass through an ostium of a sinus, at least one light emitting element in the distal end portion, and at least one structure extending from a proximal end of the device through the proximal end portion and at least part of the distal end portion to connect the at least one light emitting element with a power source.

In at least one embodiment, the illuminating device comprises an illuminating guidewire.

In at least one embodiment, the illuminating device comprises an ostium seeker device, and the distal end portion is rigid or malleable.

In at least one embodiment, the illuminating device comprises an ostium seeker device, and the distal end portion comprises a ball tip at a distal end thereof.

In at least one embodiment, the illuminating device comprises a sinus suction instrument, and the distal end portion further comprises a suction lumen configured and adapted to apply suction therethrough.

In at least one embodiment, the illuminating device comprises an integrated wire dilatation catheter, wherein an integrated illuminating guidewire extends distally of a distal end of a dilatation catheter of the device.

An illuminating guidewire device is provided including: a guidewire including an elongated main body having a flexible distal end portion and a relatively less flexible proximal end portion; at least one light conducting channel extending the length of the elongated body, and configured and dimensioned to deliver light from a proximal end of the guidewire to a distal end of the guidewire and to emit light from the distal end of the guidewire.

In at least one embodiment, the at least one light conducting channel comprises at least one illumination fiber.

In at least one embodiment, the at least one light conducting channel comprises at least two illumination fibers.

In at least one embodiment, the illumination fibers are formed of plastic.

In at least one embodiment, the at least one illumination fiber is formed of glass.

In at least one embodiment, the at least one light conducting channel comprises at least one laser fiber.

In at least one embodiment, a quick release connector is mounted over at least part of the proximal end portion of the elongated body, and is adapted to be connected to a light channel extending from a light source; and to quickly connect to and release from the proximal end portion of the elongated body.

In at least one embodiment, the quick release connector is optically coupled with the light source.

In at least one embodiment, a proximal end portion of the connector comprises a tapering light channel configured to adapt a relatively larger inside diameter of the light channel to a relatively smaller diameter of the proximal end of the elongated body.

In at least one embodiment, a proximal end portion of the quick release connector is adapted to connect with a light source. In at least one embodiment, the proximal end portion of the quick release connector includes an ACMI light post.

In at least one embodiment, the connector is rotatable with respect to the light channel extending from the light source, when the connector is connected to the light channel.

In at least one embodiment, the distal end portion of the connector comprises an opening configured to slidably receive the proximal end portion of the elongated body, and a quick release locking mechanism is configured to fix the proximal end portion received in the connector.

In at least one embodiment, the quick release locking mechanism, in a locked configuration, maintains a proximal end of the elongated body in alignment with a distal end of the tapering light channel of the connector.

In at least one embodiment, the quick release locking mechanism is movable between an unlocked configuration in which the proximal end portion can be slid from the connector to disconnect therefrom, and a locked configuration that maintains the proximal end portion in connection with the connector.

In at least one embodiment, a core wire extends at least within the distal end portion of the elongated body of the guidewire. In at least one embodiment, the core wire further extends within the proximal end portion.

An illuminating guidewire device is provided, including: a guidewire having an elongated main body with a flexible distal end portion and a relatively less flexible proximal end portion; a light emitting diode mounted in the distal end portion and configured to emit light from a distal tip of the distal end portion; and at least one electrical wire extending the length of the elongated body, being electrically connected to the light emitting diode, and extending proximally of a proximal end of the elongated body.

In at least one embodiment, the illuminating guidewire device includes at least two such electrical wires.

In at least one embodiment, a core wire extends at least within the distal end portion of the elongated body. In at least one embodiment, the core wire further extends within the proximal end portion.

In at least one embodiment, a radiopaque marker is provided on the distal end portion. In at least one embodiment, an electromagnetic coil is provided on the distal end portion.

An illuminating guidewire device is provided, including: a guidewire having a flexible distal end portion, a relatively less flexible proximal end portion, and a transparent portion interconnecting the distal and proximal end portions; at least one light emitting element mounted in the guidewire and configured to emit light through the transparent portion; and at least one structure extending from a proximal end of the device through the proximal end portion and connecting with the at least one light emitting element.

In at least one embodiment, the transparent portion comprises a clear tube.

In at least one embodiment, the clear tube includes cut out windows therein.

In at least one embodiment, the transparent portion comprises a plurality of struts interconnecting the proximal and distal end portions of the guidewire.

In at least one embodiment, a deflector is mounted distally of the at least one light emitting element in the transparent portion.

In at least one embodiment, a quick release connector is mounted over at least part of the proximal end portion, and is adapted to be connected to a light channel extending from a light source, and to quickly connect to and release from the proximal end portion of the guidewire.

In at least one embodiment, a core wire extends at least within the distal end portion. In at least one embodiment, the core wire further extends within the proximal end portion.

A quick release connector for use with an illuminating guidewire is provided to include: a main body having a proximal end portion and a distal end portion; a channel in the distal end portion and opening to a distal end of the main body, wherein the channel is configured and dimensioned to slidably receive a proximal end portion of the illuminating guidewire; and a quick release locking mechanism configured to assume a locked position and an unlocked position, wherein when in the locked position, the quick release locking mechanism fixes the proximal end portion of the illuminating guidewire in the channel.

In at least one embodiment, the quick release locking mechanism is biased to the locked position.

In at least one embodiment, upon inserting the proximal end portion of the illuminating guidewire into the channel, the proximal end portion contacts portions of the quick release locking mechanism, driving the portions apart to allow the proximal end portion to be slid into the channel.

In at least one embodiment, the quick release locking mechanism comprises a locking arm that extends into the channel and a portion that extends out of the housing, wherein the portion extending out of the housing is manually retractable to move the locking arm from the locked position to the unlocked position.

In at least one embodiment, the quick release locking mechanism includes at least two locking arms provided circumferentially about the distal end portion of the main body of the connector.

In at least one embodiment, the quick release locking mechanism comprises a pin vise.

In at least one embodiment, the proximal end portion of the connector is adapted to be connected to a light channel extending from a light source.

In at least one embodiment, the proximal end portion of the main body is optically coupled with a light source.

In at least one embodiment, the proximal end portion of the main body includes a tapering light channel configured to adapt a relatively larger inside diameter of a light channel to a relatively smaller diameter of the proximal end of the illuminating guidewire.

In at least one embodiment, the proximal end portion of the main body comprises an ACMI light post.

In at least one embodiment, the quick release connector is rotatable with respect to a light channel extending from a light source, when the connector is connected to the light channel.

These and other advantages and features of the invention will become apparent to those persons skilled in the art upon reading the details of the devices, methods and systems as more fully described below.

Other features and advantages will become apparent from the following detailed description, taken in conjunction with the accompanying drawings, which illustrate by way of example, the features of the various embodiments.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is an illustration of a patient being treated by a system for catheter-based minimally invasive sinus surgery according to prior art techniques.

FIGS. 2A through 2D are illustrations of partial sagittal sectional views through a human head showing various steps of a method of gaining access to a paranasal sinus using a sinus guide.

FIG. 3 illustrates a scope introduced on the side of the sinus guide.

FIG. 4 shows an illuminating guidewire according to one embodiment of the present invention.

FIG. 5 shows a distal end portion of a guidewire having a bent shape.

FIG. 6 is a cross-sectional illustration of a distal end portion of a guidewire device showing a core wire fixed to the coil.

FIG. 7 shows a cross-sectional view of a guidewire device that includes a fiber optic bundle of light fibers.

FIG. 8 shows an illuminating guidewire according to another embodiment of the present invention.

FIG. 9 is a cross-sectional illustration of a distal end portion of the guidewire shown in FIG. 8.

FIG. 10 shows an illuminating guidewire according to another embodiment of the present invention.

FIG. 11 illustrates an alternative transparent portion that may be included in a device shown in FIG. 10.

FIG. 12 illustrates another alternative transparent portion that may be included in a device shown in FIG. 10.

FIG. 13A illustrates an illuminating guidewire device including a quick release connector that is optically coupled to a light source.

FIG. 13B is a view of the arrangement of FIG. 13A in which the quick release locking mechanism is in the locked position.

FIG. 14A illustrates an alternative quick release connector.

FIG. 14B illustrates the connector of FIG. 14A mounted over a proximal end portion of an illuminating guidewire.

FIG. 15 illustrates another alternative quick release connector.

FIG. 16 illustrates another alternative quick release connector.

FIGS. 17A-17E are illustrations of partial coronal sectional views through a human head showing various steps of a method for treating an ostium that opens to a frontal sinus.

FIG. 18 illustrates a situation, like that described with regard to FIG. 3, where a scope has been inserted as far as possible without causing significant trauma to the patient. Additionally, FIG. 18 shows an illuminating guidewire having been extended distally of the limit of illumination of the scope, to effectively extend the illumination distance viewable by the scope.

FIG. 19 illustrates non-limiting examples of where one or more filters may be placed in an illuminating guidewire device.

FIG. 20A schematically illustrates a connector having a rotating shutter rotatably mounted therein.

FIG. 20B is an illustration of a plan view of the shutter of FIG. 20A.

FIG. 21 shows a frontal ostium seeker instrument that can be used to access a sinus ostium.

FIG. 22 shows a suction sinus instrument that is configured to evacuate blood and/or other fluids from a target surgical site, such as the frontal sinus.

FIG. 23 shows an integrated wire dilatation catheter 120 that includes an elongate, flexible catheter shaft having a balloon mounted thereon.

FIG. 24 shows a length of another embodiment of an illuminating guidewire.

FIG. 25 shows a cross-sectional view of the illuminating guidewire of FIG. 24.

FIG. 26 depicts a cross-sectional view of a preferred cable tube.

FIG. 27 shows another embodiment of a core wire.

FIG. 28 shows yet a further embodiment of a core wire.

FIG. 29 illustrates in cross-section, an enlarged view of the assembly depicted in FIG. 25;

FIG. 30 illustrates in cross-section another approach of fixing a core wire within a cable tube.

FIG. 31 shows yet another approach to configuring a core wire within a cable tube.

FIG. 32 depicts an exterior of a connection assembly.

FIG. 33 illustrates in cross-section the connector assembly of FIG. 32.

FIG. 34 shows a cross-sectional view of an alternative connector assembly.

FIG. 35 illustrates yet another embodiment of a connector assembly in cross-section.

FIG. 36 shows a lateral cross-section view of the connector assembly of FIG. 35.

FIG. 37 illustrates an illuminating guidewire according to one embodiment of this invention.

FIG. 37A-A shows a cross section of the guidewire of FIG. 37 at point A-A in the distal coil region.

FIG. 37B-B shows a cross section of the guidewire of FIG. 37 at point B-B in the proximal coil region.

FIG. 37C-C shows a cross section of the guidewire of FIG. 37 at point C-C in the distal cable tube region.

FIG. 37D-D shows a cross section of the guidewire of FIG. 37 at point D-D in the proximal cable tube region.

FIG. 37E-E shows a cross section of the guidewire of FIG. 37 at point E-E in the distal hypotube region.

FIG. 37F-F shows a cross section of the guidewire of FIG. 37 at point F-F in the proximal hypotube region.

FIG. 38 is a cross section view of the illuminated guidewire of FIG. 37.

FIG. 38A is a detailed view of area A of the guidewire of FIG. 38.

FIG. 38B is a detailed view of area B of the guidewire of FIG. 38.

FIG. 38C is a detailed view of area C of the guidewire of FIG. 38.

FIG. 39 shows cross-sectional view of an alternative connector assembly.

FIG. 39A illustrates a detailed view of the proximal end of the connector of FIG. 39.

DETAILED DESCRIPTION

The present disclosure provides an apparatus and method which eliminates or reduces a need for remote imaging techniques. To accomplish this, there is disclosed a medical device having desirable pushability and torquability so that an interventional site is accessed. The disclosed medical device embodies structure or includes components which are pre-treated so that it can accommodate forces applied thereto during operation.

Before the present devices and methods are described, it is to be understood that this invention is not limited to particular embodiments described, as such may, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting, since the scope of the present invention will be limited only by the appended claims.

Where a range of values is provided, it is understood that each intervening value, to the tenth of the unit of the lower limit unless the context clearly dictates otherwise, between the upper and lower limits of that range is also specifically disclosed. Each smaller range between any stated value or intervening value in a stated range and any other stated or intervening value in that stated range is encompassed within the invention. The upper and lower limits of these smaller ranges may independently be included or excluded in the range, and each range where either, neither or both limits are included in the smaller ranges is also encompassed within the invention, subject to any specifically excluded limit in the stated range. Where the stated range includes one or both of the limits, ranges excluding either or both of those included limits are also included in the invention.

Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. Although any methods and materials similar or equivalent to those described herein can be used in the practice or testing of the present invention, the preferred methods and materials are now described. All publications mentioned herein are incorporated herein by reference to disclose and describe the methods and/or materials in connection with which the publications are cited.

It must be noted that as used herein and in the appended claims, the singular forms “a”, “an”, and “the” include plural referents unless the context clearly dictates otherwise. Thus, for example, reference to “a tube” includes a plurality of such tubes and reference to “the shaft” includes reference to one or more shafts and equivalents thereof known to those skilled in the art, and so forth.

The publications discussed herein are provided solely for their disclosure prior to the filing date of the present application. Nothing herein is to be construed as an admission that the present invention is not entitled to antedate such publication by virtue of prior invention. Further, the dates of publication provided may be different from the actual publication dates which may need to be independently confirmed.

Turning now to FIG. 1, an illustration of a patient being treated by a system for catheter-based minimally invasive sinus surgery according to prior art techniques is shown. A C-arm fluoroscope 1000 that is useable to visualize a first introducing device 1002 (e.g., a sinus guide, guide catheter or guide tube), a second introducing device 1004 (e.g., a guidewire or elongated probe) and a working device 1006 (e.g., a balloon catheter, other dilatation catheter, debrider, cutter, etc.). The sinus guide, guide catheter or guide tube 1002 may be introduced under direct visualization, visualization provided by fluoroscope 1000 and/or from endoscopic visualization, to place the distal end of catheter or tube 1002 at a location approaching an ostium of a sinus to be treated.

Next guidewire or elongated probe 1004 is inserted through catheter or tube 1002 and distally advanced to extend the distal end of guidewire or elongated probe through the ostium to be treated and into the sinus that the ostium opens to. Proper placement often involves advancement and retraction of the distal end of guidewire or elongated probe, under fluoroscopic visualization, until it has been visually confirmed that the distal end of the guidewire or elongated probe is located where the surgeon believes the appropriate sinus to be located, relative to the other features of the patient's head that are visualized under fluoroscopy.

Once guidewire or elongated probe 1004 has been properly placed, working device 1006 is next passed over the guidewire or elongated probe 1004, under visualization via fluoroscope 1000 and/or an endoscope (not shown) that has been inserted adjacent catheter or tube 1002, to place the working end of working device 1006 in the target location where a surgical procedure is to be performed. Typically, the guidewire or elongated probe remains in place during the procedure. Under the same type(s) of visualization, the working (distal) end of working device is then actuated to perform the desired surgical procedure. In the case of a dilatation catheter, the balloon at the distal end portion of catheter 1006 is expanded once it has been located across the ostium. This expansion acts to open the ostium to allow proper mucus flow, as was described in more detail above.

After performance of the desired surgical procedure, the working device 1006 is deactivated and withdrawn from the patient, after which the remaining devices are withdrawn to complete the procedure.

By using the devices and methods described herein, at least the need for fluoroscopic visualization of the placement of the guidewire/elongated probe can be reduced or eliminated. Further optionally, all fluoroscopic visualization needs may be eliminated in some surgical circumstances.

It is to be appreciated that the devices and methods of the present invention relate to the accessing and dilatation or modification of sinus ostia or other passageways within the ear, nose and throat. These devices and methods may be used alone or may be used in conjunction with other surgical or non-surgical treatments, including but not limited to the delivery or implantation of devices and drugs or other substances as described in co-pending U.S. patent application Ser. No. 10/912,578.

FIGS. 2A through 2D are illustrations of partial sagittal sectional views through a human head showing various steps of a method of gaining access to a paranasal sinus using a sinus guide. In FIG. 2A, a first introducing device in the form of a sinus guide 1002 is introduced through a nostril and through a nasal cavity 1012 to a location close to an ostium 1014 of a sphenoid sinus 1016. Sinus guide 1002 may be straight, malleable, or it may incorporate one or more preformed curves or bends as further described in U.S. Patent Publication Nos. 2006/004323; 2006/0063973; and 2006/0095066, for example, each of which are incorporated herein, in their entireties, by reference thereto. In embodiments where sinus guide 1002 is curved or bent, the deflection angle of the curve or bend may be in the range of up to about 135 degrees.

In FIG. 2B, a second introduction device comprising a guidewire 10 is introduced through the first introduction device (i.e., sinus guide 1002) and advanced so that the distal end portion of guidewire 10 enters the sphenoid sinus 1016 through the ostium 1014.

In FIG. 2C, a working device 1006, for example a balloon catheter, is introduced over guidewire 10 and advanced to extend the distal end portion of device 1006 into the sphenoid sinus 1016. Thereafter, in FIG. 2D, working device 1006 is used to perform a diagnostic or therapeutic procedure. In this particular example, the procedure is dilatation of the sphenoid sinus ostium 1014, as is illustrated in FIG. 2D, where the balloon of device 1006 is expanded to enlarge the opening of the ostium 1014. After completion of the procedure, sinus guide 1002, guidewire 10 and working device 1006 are withdrawn and removed. It will be appreciated that the present invention may also be used to dilate or modify any sinus ostium or other man-made or naturally occurring anatomical opening or passageway within the nose, paranasal sinuses, nasopharynx or adjacent areas. As will also be appreciated by those of ordinary skill in the art, in this or any of the procedures described in this patent application, the operator may additionally advance other types of catheters, and that guidewire 10 may be steerable (e.g. torqueable, actively deformable) or shapeable or malleable.

FIGS. 2B-2D show an optional scope 1008 in dotted lines, that may be inserted to provide visualization of advancement of sinus guide 1002 and/or inserted alongside catheter 1006 to provide visualization of all or at least a portion of working tool 1006. It is to be appreciated that optional scope 1008 may comprise any suitable types of rigid or flexible endoscope and such optional scope may be separate from or incorporated into the working devices and/or introduction devices of the present invention, as further described in provisional Application Ser. No. 60/844,874 titled “Endoscopic Methods and Devices for Transnasal Procedures, which is hereby incorporated herein, in its entirety, by reference thereto.

Although scope 1008 may be useful to reduce or eliminate the need for fluoroscopic visualization during placement of sinus guide 1002 and/or for visualization of the procedure performed by working device 1006, it does not provide stand-alone capability to see inside the sinus (e.g., sphenoid sinus 1016 or other sinus of interest), and therefore cannot provide sufficient visual feedback for use in guiding guidewire 10 into the desired sinus (e.g., frontal sinus, or some other sinus of interest) or sufficient visual image confirmation of correct placement of guidewire 10 into the desired sinus.

Further, depending upon the particular configuration of the sinus passageways to be traversed to gain access to a target ostium, the scope 1008, due to physical limitations (e.g., outside diameter, degree of rigidity, etc.) may be unable to visualize as deep as the location of the ostium of interest. For example, FIG. 3 illustrates a situation where scope 1008 has been inserted as far as possible without causing significant trauma to the patient. The range of adequately illuminated visibility in this case does not extend all the way to ostium 1020, as indicated schematically by the rays 1009 shown extending distally from scope 1008. In this case, adequately illuminated visualization of guidewire 10 into ostium 1020 would not be possible via scope 1008. Additionally, if sinus guide 1002 is physically capable of being extended further distally to place the distal end thereof at the approach to ostium 1020, scope 1008 would also not be capable of adequately visualizing this. Thus, prior to the current invention, fluoroscopic or other x-ray visualization of these procedures was required, in order to ensure that the devices approach (and extend through) the appropriate ostium 1020 and not another adjacent opening, such as opening 1024.

In order to overcome these and other problems, the guidewire devices 10 of the present invention include their own light emitting capability. By illuminating a distal end portion of guidewire 10, a process known as transillumination occurs as guidewire 10 traverses through the sinus passageways, passes through an ostium and enters a sinus cavity. Transillumination refers to the passing of light through the walls of a body part or organ. Thus, when guidewire 10 is located in a sinus, the light emitted from guidewire 10 passes through the facial structures and appears as a glowing region on the skin (e.g., face) of the patient. It is noted that the light emitted from scope 1008, such as positioned in FIG. 3, for example, results in transillumination as well, but the resultant glow is much more diffuse and larger in area. As the light source in guidewire 10 gets closer to the surface of the structure that it is inserted into (e.g., the surface of the sinus), the transillumination effect becomes brighter and more focused (i.e., smaller in area). Additionally, the movements of the guidewire 10 can be tracked by following the movements of the transillumination spot produced on the skin of the patient. These concepts have been described in co-pending U.S. patent application Ser. No. 12/122,884, entitled “Sinus Illumination Lightwire Device” and in U.S. Pat. No. 7,559,925, which are hereby incorporated herein, in their entirety, by reference thereto.

FIG. 4 shows an illuminating guidewire 10 according to one embodiment of the present invention. Device 10 includes a flexible distal end portion 10 d that provides a similar degree of flexibility to a standard, non-illuminating type of guidewire. Distal end portion 10 d may include a coil 10 c as an exterior portion thereof, to help provide the desired flexibility to this portion. The proximal end portion 10 p of device 10 extends the device to provide a sufficient length so that device 10 extends proximally out of the patient (and, when inserted through another device, such as a sinus guide, proximally out of the device into which guidewire 10 is inserted), at all times, including the deepest location into which the distal end of device 10 is placed. The proximal end portion 10 p can have visible markings, preferably spaced at equal intervals that can be observed by the user to confirm how far the guidewire 10 has been placed in the patient. Proximal end portion 10 p also provides the necessary mechanical properties required to make the guidewire function properly. These mechanical properties include torquability, i.e., the ability to torque the proximal end portion 10 p from a location outside of the patient and have that torque transmitted to the distal end portion 10 d; pushability, i.e., sufficient rigidity, so that when an operator pushes on the proximal end portion 10 p from a location outside of the patient, the pushing force transmits to the distal portion 10 d to advance the distal portion 10 d without buckling the device 10; and tensile strength so that an operator can pull on the proximal end portion 10 p from a location outside of the patient and withdraw device 10 from the patient without significant plastic deformation or any disintegration of the device.

Coil 10 c may be formed from a stainless steel wire, for example. The diameter of the coil wire can be between about 0.004 and about 0.008 inches, typically about 0.006 inches. Alternative materials from which coil 10 c may be formed include, but are not limited to: ELGILOY®, CONICHROME® or other biocompatible cobalt-chromium-nickel alloy; nickel-titanium alloys, or other known biocompatible metal alloys having similar characteristics. Further alternatively, the distal end portion may comprise a braided metallic construction of any of the aforementioned materials in lieu of a coil.

The external casing of the proximal portion 10 p can be made from a polyimide sheath, a continuous coil (optionally embedded in polymer or having polymer laminated thereon), a hypotube (e.g., stainless steel hypotube), a laser-cut hypotube, a cable tube, or a tube made from PEBAX® (nylon resin) or other medical grade resin. In any of these cases the construction needs to meet the required torquability, pushability and tensile requirements of the device.

In the example shown, coil 10 c is joined to proximal portion 10 p by solder, epoxy or other adhesive or mechanical joint. One or more illumination channels 10i are provided in device 10 and extend the length thereof. Illumination channels 10 i are configured to transport light from the proximal end of device 10 to and out of the distal end of device 10. In the example shown, two illumination channels are provided, each comprising a plastic illumination fiber. The plastic used to make the illumination fibers is compounded for light transmission properties according to techniques known and available in the art. As one example, ESKA™ (Mitsubishi Rayon), a high performance plastic optical fiber may be used, which has a concentric double-layer structure with high-purity polymethyl methacrylate (PMMA) core and a thin layer of specially selected transparent fluorine polymer cladding. In one example, illumination fibers each have an outside diameter of about 0.010″. The illumination fibers can have an outside diameter in the range of about 0.005 inches to about 0.010 inches.

Alternatively, a single plastic illumination fiber 10 i may be used that has an outside diameter of about 0.020″. Further alternatively, glass illumination fibers may be substituted which are much smaller in outside diameter, e.g., about 0.002″. In this case, more illumination fibers may be provided in a bundle, e.g., about six to fifty glass fibers 10 i may be provided.

The distal end of device 10 is sealed by a transparent (or translucent) seal 10 s which may be in the form of epoxy or other transparent or translucent adhesive or sealing material. Seal 10 s maintains the distal ends of illumination fibers 10 i coincident with the distal end of device 10 and also provides an atraumatic tip of the device 10. Further, seal 10 s prevents entrance of foreign materials into the device. The distal end can be designed to either focus or distribute the light as it emanates therefrom, to achieve maximum transillumination effects. In this regard, the distal end can include a lens, prism or diffracting element.

The proximal end of device 10 is also sealed by a transparent (or translucent) seal 10 ps which may be in the form of epoxy or other transparent or translucent adhesive or sealing material. Seal 10 ps maintains the proximal ends of illumination fibers 10 i coincident with the proximal end of device 10. The proximal end of device 10 may be further prepared by grinding and polishing to improve the optical properties at the interface of the proximal end of device 10 with a light source. The illumination fibers 10 i at locations intermediate of the proximal and distal ends need not be, and typically are not fixed, since no mapping of these fibers is required, as device 10 provides only illumination, not a visualization function like that provided by an endoscope. Further, by leaving illumination fibers free to move at locations between the proximal and distal ends, this increases the overall flexibility and bendability of device 10 relative to a similar arrangement, but where the illumination fibers 10 i are internally fixed.

The outside diameter of device 10 may be in the range of about 0.025 inches to about 0.040 inches, typically about 0.030 to 0.038 inches, and in at least one embodiment, is about 0.035″±0.005″. At least the distal portion 10 p of device 10 is provided with a core wire 10 cw that is contained therein. In the example shown in FIG. 4, core wire 10 cw is a wire that is fixed to proximal section 10 p such as by laser welding, epoxy or other adhesive or mechanical fixture. Core wire 10 cw may extend substantially the full length of device 10. In any case, core wire 10 cw is typically formed from stainless steel NITINOL (nickel-titanium alloy) or other biocompatible nickel-titanium alloys, cobalt-chromium alloys, or other metal alloys that are biocompatible and provide the necessary rigidity and torquability. Core wire 10 cw may be formed as a wire, as in the example shown in FIG. 4, or alternatively, may be braided from any of the same materials or combination of materials mentioned above. Core wire 10 cw, when formed as a wire can be ground to different diameters to provide varying amounts of rigidity and torquability. When formed as a braid, the braid can be formed to have varying amounts of rigidity and torquability along the length thereof. For example, core wire 10 cw has a larger outside diameter at the proximal end portion than at the distal end portion so that it is more rigid and transfers more torque from the proximal portion of device 10, whereas at the distal end portion, core 10 cw is relatively more flexible and twistable. For core wires 10 cw that extend through proximal portion 10 p, the portion of core wire near the proximal end of device 10 may have an even larger outside diameter.

Core wire 10 cw particularly increases the pushability and the torquability of coil 10 c which, by itself, is quite flexible and twistable. Combined with core wire 10 cw, the distal portion is much more effective at transferring pushing and torquing forces without buckling or twisting. Additionally, core wire 10 cw may be plastically deformed or memory set into a bent shape, an example of which is shown in FIG. 5. Bend 10 b provides a steerability function, allowing an operator to direct the distal end of device 10 in different directions by torquing device about the longitudinal axis of the device, as indicated by the arrows in FIG. 5. In some embodiments this bending can be performed by an operator in the midst of a procedure, which can be particularly useful in combination with a scope 1008, as viewing through the scope may make it apparent to the operator that the guidewire 10 needs to be inserted or directed at an angle offset from where the straight direction along the longitudinal axis of the device would direct it to. In some embodiments, the guidewire 10 does not have a core wire. In these embodiments, the outer jacket (e.g., a coil, cable tube, laser-cut hypotube, braided polymer tube, etc.) provides the support for torque, pushability and tension. An advantage of not having a core wire is that the full inner diameter of the guidewire is then available to be filled with illumination fibers.

The illumination fibers, as noted above, can be free to move about radially within the device. Further, there is no need to center the illumination fibers 10 i with respect to device 10 even at the distal and proximal ends of the device. FIG. 6 is a sectional illustration of a distal end portion of device 10 showing core wire 10 cw fixed to coil 10 c, with illumination fibers 10 i residing adjacent to core wire 10 cw, but not fixed to either core wire 10 cw or coil 10 c.

The plastic or glass illumination fibers 10 i of the device shown in FIG. 4 are typically used to transmit light from a light source such as one provided in an operating room for use by endoscopes, e.g., xenon light source, halogen light source, metal halide light source, etc. Alternatively, device 10 may be configured to transmit light from other light sources, such as a laser light source, wherein laser fibers 10 f would be substituted for the illumination fibers described above, and extend through device 10 in a fiber optic bundle as illustrated in the cross-sectional view of FIG. 7. The fiber optic bundle, like the illumination fibers 10 i, contributes to stiffness (in both bending and torquing motions) of device 10, thereby enhancing trackability, steering and other torquing.

FIG. 8 illustrates another embodiment of an illuminating guidewire 10. In this example, proximal end portion of device 10 is formed externally by a coil with a polymer layer laminated thereon, but any of the other arrangements described above may be substituted. In this example, illumination is provided by a high intensity light emitting diode (LED) 10 id fitted at the distal end of device 10. The proximal end of device 10 may be sealed such as with epoxy, or any of the other alternatives mentioned above with regard to the proximal end of device 10 in FIG. 4, in order to prevent pulling on the wires 10 w at the connections with LED 10 id, as well as to seal the proximal end of the device. Grinding and polishing are not necessary, as the proximal end of device 10 in FIG. 8 does not transmit light.

Device 10 in FIG. 8 performs substantially similar to the device 10 of FIG. 4 with regard to the properties of pushability, torquability and tensile properties. Device 10 of FIG. 8, however, does not require illumination fibers or laser fibers. Instead, a pair of insulated lead wires are electrically connected to the terminals of LED 10 id (not shown) and then extend within device 10 over the length of device 10 to extend proximally from the proximal end of device 10. The free ends of wires 10 w are configured to be connected to a power source that functions as the source of electrical power, to deliver electrical energy to LED 10 id to illuminate it. FIG. 9 illustrates a cross-sectional view of a distal end portion of device 10 of FIG. 8. In this example, core wire 10 cw is in the form of a flattened distal end core wire or shaping ribbon as known in the art, that extends between the two wires 10 w. FIG. 9 also illustrates the insulation layer 10 iw over each wire.

Any of the devices 10 described herein may optionally include one or more radiopaque markers and/or electromagnetic coils on the tip of the device 10 and/or elsewhere along the device for enhancing visibility by fluoroscopy systems, image guided surgery (IGS) systems, or other visualization systems.

FIG. 10 shows an alternative design of device 10 in which light is emitted proximally of the distal end of the device. This configuration may employ any of the various light transmission means described above (e.g., illumination fibers, laser fibers, LED). The proximal portion 10 p may be constructed in any of the manners described above with regard to other embodiments of device 10. The distal portion 10 d includes a transparent proximal end portion 10 dp that mounts over the distal end of proximal end portion 10 p of the device 10. The transparent portion 10 dp permits the illumination emitted from illumination member 10 i or 10 id to pass out of the device 10 at the location of transparent portion 10 dp. The illumination member(s) 10 i or 10 id thus terminate at the proximal end portion 10 dp of the distal end portion of device 10. Distally of this transparent portion 10 dp, the distal portion 10 dd of distal end portion 10 d of device 10 extends as a floppy guidewire leader or tip. This floppy guidewire leader or tip 10 dd may include a coiled section 10 c and may optionally include a core wire 10 cw in the manner described above with regard to FIG. 4. The light emitted from illumination fibers will disperse naturally through the transparent portion 10 dp. Optionally, a deflector 11, such as a convex mirror (e.g., parabolic or other convex) shape or other reflective surface may be provided distally of illumination fibers/light emitting portion 10 i, 10 id of device 10 to deflect light rays out of the transparent portion. Additionally, or further alternatively, illumination fibers 10 i may be angled at the distal end portions thereof to direct the emitted light out through the transparent portion.

This configuration may be beneficial in further protecting the illumination emitter(s) 10 i, 10 id from foreign materials inside the body, as well as from trauma that may be induced by bumping the illumination emitter up against structures within the body. Further, a floppy guidewire leader 10 dd of this type may provide more flexibility and maneuverability than a device in which the illumination emitter is located on the distal tip of the device.

Transparent portion 10 dp may be provided as a clear plastic or glass integral tube, or may have openings or windows 10 t provided therein (see the partial view of FIG. 10). Further alternatively, transparent portion may be formed by a plurality of struts 10 st circumferentially arranged to interconnect the distal floppy tip 10 dd with the proximal end portion 10 p of device 10 as shown in the partial illustration of FIG. 12. Alternatively members 10 st may be intersecting in a criss-crossing cage like configuration or other cage configuration. In any of these alternative configurations, members 10 st may be transparent, but need not be and could be formed of non-transparent materials, such as metals or opaque plastics, for example.

Device 10 should be readily connectable to and disconnectable from a power source to enable attachment for providing illumination for positioning the guidewire 10 and/or other devices during a procedure, detachment to allow another device to be slid onto the guidewire 10 from a free proximal end thereof, and reattachment to again provide illumination, to assist in guidance/visualization of the device being passed over the guidewire 10, for example.

FIGS. 13A and 13B illustrate one example of a coupler 20 that is configured for quick connection and disconnection of an illumination guidewire 10 that employs illumination fibers 10 i or laser fibers 10 f. Coupler 20 is connected to a light source 1030, such as a conventional endoscope light source, for example, or other light source capable of delivering preferably at least 10,000 lux through coupler 20. Light cable 1032 optically connects connector 20 with light source 1030 to deliver light from the light source 1030 to connector 20. Light cable 1032 can optionally be a fluid-filled light cable, such as the type provided with DYMAX BlueWave™ 200 and ADAC Systems Cure Spot™ light cables, for example. A liquid filled light cable comprises a light conducting liquid core within plastic tubing. The liquid is non-toxic, non-flammable and transparent from 270 to 720 nm. The ends of a liquid filled light cable can be sealed with high quality quartz glass and metal spiral tubing surrounded by a plastic sleeve for exterior protection.

Connector 20 includes a proximal channel, slot or bore 22 that has an inside dimension or circumference that is slightly greater than the outside diameter or circumference of device 10 at the proximal end portion 10 p. A quick release locking mechanism 24 is provided for locking and unlocking device 10 within connector 20. Quick release locking mechanism 24 is biased toward the locking position shown in FIG. 13B, in which the locking portion 24 a of mechanism 24 is driven into channel slot or bore 22 and may even abut against the opposite wall of the channel, slot or bore 22, when no guidewire 10 has been inserted. Locking mechanism 24 may be spring-biased toward the locked position, for example. Additionally, locking mechanism 24 may include a ball and detent arrangement, or other temporary locking means to maintain the mechanism 24 in the locked configuration. An additional, similar mechanism may be provided to temporarily fix locking mechanism 24 in the unlocked configuration shown in FIG. 13A. Alternative locking mechanisms may be employed, such as a pivoting lock arm, for example, that is manually pivotable between the locked and unlocked orientations, or other mechanism that would be apparent to one of ordinary skill in the mechanical arts, such as a collapsible silicone valve that grips the device, for example.

Light cable 1032 generally has a much larger inside diameter than the inside diameter or combined inside diameters of the illumination fibers 10 i. Accordingly, the proximal end portion of connector 20 provides a tapering or funnel shaped pathway 26 having a proximal inside diameter that is substantially equivalent to the inside diameter of cable 1032 or greater, and which tapers to a distal inside diameter that is about the same or only slightly greater than the inside diameter or combined inside diameters of the illumination fiber(s), or alternatively, that is about the same or only slightly greater than the outside diameter of the proximal end of device 10. The light cable 1032 generally has a larger diameter bundle of illumination fibers than that contained within the illuminating guidewire 10. Accordingly, the taper 26 is used to transition between the larger bundle in the light cable 1032 and the smaller bundle in the guidewire 10 With this arrangement, light delivered through light cable 1032 is concentrated or focused down to a pathway where most of the light can be transmitted through the illumination fibers.

To insert device 10 into connector 20, an operator retracts quick connect locking mechanism 24 to the open position shown in FIG. 13A. If quick connect mechanism 24 is provided with a temporary locking mechanism as referred to above, then quick connect locking mechanism 24 can be temporarily fixed in the orientation shown in FIG. 13A, without the operator having to hold it open. Otherwise, the operator will hold connector 20 open in the position shown in FIG. 13A. The proximal end of device 10 is next inserted into the open channel, slot or bore 22 and slid proximally with respect to connector 20 until the proximal end of device 10 abuts against the proximal end of channel, slot or bore 22. Quick release mechanism is next released by the operator (in embodiments when there is no temporary locking mechanism to maintain the quick release in the open configuration) or released from the temporary locked open configuration, so that the locking arm 24 a is advanced toward the proximal end portion 10 p of device 10, by the biasing of quick connect locking mechanism 24 described above. Locking arm 24 a contacts device 10 and holds device 10 under compression between locking arm 24 a and the opposite inner wall of channel, slot or bore 22, with sufficient force to prevent device 10 from sliding out of connector 20 even if the distal tip of device 10 is pointed straight down in a vertical direction. Optionally, locking arm 24 a may be additionally temporarily locked in place by a ball and detent mechanism, or other temporary locking mechanism, as mentioned above. To remove device 10 from connector 20, quick connect locking mechanism 24 is repositioned to the open or unlocked orientation shown in FIG. 13A and the device is slid distally with respect to the connector until it is free from the connector 20.

FIGS. 14A-14B illustrate an alternative connector 20 that includes a quick release locking mechanism 24. In this example, two or more locking arms 24 a are provided circumferentially about the distal end of connector 20. Arms 24 a are biased to the closed or locked configuration as shown in FIG. 14A. For example, arms 24 a may be made from resilient spring steel, nickel-titanium alloy or resilient plastic and formed to assume the configuration shown in 14A when mounted to connector 20 and when in an unbiased state. Installation of device 10 into connector 20 is simplified by the automatic grasping and temporary locking functions provided by quick release locking mechanism 24. The proximal end of device 10 is simply inserted between the two or more arms 24 a. Arms 24 a include ramped or cammed surfaces 24 b that guide the proximal end of device 10 into connector 20, and, as device 10 is pushed against these surfaces 24 b, arms 24 a are deflected into the opened, biased configuration shown in FIG. 14B. The biasing/resiliency of arms 24 a imparts compressive forces to the shaft of device 10 via temporary locking surfaces 24 a, so that device 10 is gripped and held in position as shown in FIG. 14B. To remove device 10, the operator need simply pull on device 10, while holding connector 20 relatively immobile, with a force sufficient to overcome the compressive and frictional forces imparted by arms 24 a. The resilient arms 24 a then return to the unbiased configuration shown in FIG. 14A. Optionally, arms 24 a may be coated with, or include a friction enhancing surface, such as rubber or other elastomer, and/or be roughened, such as by knurling or other surface roughening technique.

In the example shown in FIGS. 14A-14B, the light cable 1032 that is provided has an inside diameter that is about the same as the diameter of the proximal end of device 10 and thus, no tapering channel 26 is required. However, for arrangements where the light cable 1032 is much larger, as is usually the case when using a conventional endoscope light source 1030, connector 20 may be provided with a tapering light channel 26 in the same manner as described above with regard to the embodiment of FIGS. 13A-13B.

FIG. 15 illustrates a longitudinal sectional view of a connector 20 that is quickly connectable and releasable from a guidewire device 10 and is also connectable to and releasable from standard light source cables that are typically found in operating rooms. Thus, this connector 20 functions both as an adapter to connect to a conventional endoscope light source channel or cable, and as a quick release locking connector to connect to and release from a proximal end portion of guidewire 10.

The proximal end of connector 20 is provided with a light post 28 that is configured to mate with a connector on the distal end of a light cable extending from a conventional endoscope light source. For example, light post 28 may be an ACMI light post (ACMI Corporation) or other standard connector typically used to connect endoscopes to operating room light sources. Because the cable extending from an operating room light source generally has a much larger inside diameter than the inside diameter or combined inside diameters of the illumination fibers of device 10, and larger than the diameter of the proximal end of guidewire 10, the proximal end portion of connector 20 includes a light tapering or funnel-shaped pathway 26 like that described above with regard to FIG. 13A.

The quick release locking mechanism 24 in this example includes a collet 24 c that is configured to center the proximal end of device 10 with the distal end of tapering pathway 26. A threaded cap 24 d is threaded over mating threads 24 t on the body of connector 20, so that when cap 24 d is torqued in a direction to advance cap 24 d proximally with respect to the body of connector 20, inner ramped or cammed surfaces 24 e of cap 24 d ride over outer ramped or cammed surfaces 24 f of collet 24 c, thereby functioning as a pin vise and clamping collet 24 c against the proximal end portion of device 10 to clamp and maintain device 10 in its current position relative to connector 20. To insert device 10, cap 24 d is rotated in a reverse direction from that described above to open the distal opening of the inner channel 24 g of collet 24 c to a dimension larger than the outside diameter of the proximal end of device 10, so that device 10 can be easily slid through the channel 24 g until the proximal end of device 10 abuts the proximal end portion of collet 24 c, or approximates the same. The cap 24 d is then turned with respect to the body of connector 20 to clamp device 10 into position, as described above. Removal of device 10 can be performed by turning cap 24 d in a reverse direction relative to connector body 20, thereby loosening the grip of collet 24 c on device 10, after which device 10 can be easily slid out from connection with connector 20. Components of connector 20 may be made from metal, such as stainless steel or other biocompatible metals, or temperature-resistant thermosetting polymer, for example.

Light post 28 is rotatable with respect to the light cable 1032 of the light source 1030 when connector 20 is connected to the distal end connector of the light cable 1032. This allows device 10, when connected to connector 20 in this arrangement, to be rotated during use without building up significant twisting or rotational counter forces within the light cable 1032. For example, in the light post 28 shown, the female receptacle (not shown) of the light cable 1032 couples over light post 28 and engages in groove 28 g, about which the female receptacle is then rotatable relative to light post 28. FIG. 16 is a longitudinal sectional view of a connector 20 that is similar to the connector 20 described with regard to FIG. 15 above. One difference in the example of FIG. 16 is that the tapered light guide 26 is provided in the light post 28, as contrasted with being provided in the proximal end portion of the main body of connector 20 in FIG. 15. However, in both cases, the function is the same.

Turning now to FIGS. 17A-17E, illustrations of partial coronal sectional views through a human head showing various steps of a method for treating an ostium that opens to a frontal sinus are shown. The methods described here, and all other methods disclosed herein may also comprise a step of cleaning or lavaging anatomy within the nose, paranasal sinus, nasopharynx or nearby structures including but not limited to irrigating and suctioning. The step of cleaning the target anatomy can be performed before or after a diagnostic or therapeutic procedure. The methods of the present invention may also include one or more preparatory steps for preparing the nose, paranasal sinus, nasopharynx or nearby structures for the procedure, such as spraying or lavaging with a vasoconstricting agent (e.g., 0.025-0.5% phenylephyrine or Oxymetazoline hydrochloride (NEO-SYNEPHRINE or AFRIN) to cause shrinkage of the nasal tissues, an antibacterial agent (e.g., povodine iodine (BETADINE), etc. to cleanse the tissues, etc.

In FIG. 17A, a first introducing device in the form of a sinus guide 1002 is introduced through a nostril and through a nasal cavity 1012 to a location close to an ostium 1034 of a frontal sinus 1036. Sinus guide 1002 may be as described previously herein, or as described in the applications incorporated herein by reference. The advancement of sinus guide 1002 can be visualized with a scope inserted into the nasal cavity 1012 and advanced as close to the ostium 1034 as possible without causing significant trauma to the tissues therein.

Once the surgeon is satisfied that the distal end of the sinus guide 1002 is positioned close enough to the appropriate ostium 1034, illuminating guidewire 10, connected to a light source as described by any of the techniques mentioned above, is inserted through sinus guide 1002 and advanced therethrough, see FIG. 17B. There may be some transillumination from the light emitted from the scope which can be used to confirm that the sinus guide 1002 is positioned in the correct general area, which confirmation can be made even before the distal tip of guidewire 10 exits the distal end of sinus guide 1002. However, much more specific transillumination effects are produced when the tip of guidewire 10 exits the distal end of guide 1002 and especially when the light emitting portion of guidewire 10 touches or approximates an intended target surface, such as an inner wall of a sinus, for example. As the guidewire 10 is advanced, transillumination on the face of the patient can be observed as a glowing spot that moves as the distal end portion of device 10 moves, thereby making it possible to visibly track the location of the light emitting portion of device 10 without the need to use radiographic imaging, such as by fluoroscopy, for example.

As shown in FIG. 17C, a light activated drug 1037 can be injected into the patient's body. The drug 1037 can be inserted into any of the available spaces within a patient to facilitate transillumination. In one approach, the drug is injected within the sinuses for this purpose. Shining a light source upon the drug enhances the effect of the illumination device.

While there may be some diffuse transillumination on the forehead of the patient overlying the frontal sinus 1036 as the light emitting portion of device 10 approaches the ostium 1034, the glow on the forehead becomes brighter and smaller in dimension (more focused) as the light emitting portion passes through the ostium 1034 and enters the frontal sinus 1036, FIG. 17D. As device 10 is further advanced, the glowing spot becomes most defined and brightest as the light emitting portion approaches and contacts a wall of the frontal sinus 1036. Further, as noted, the movement of the transilluminated spot can be visibly followed to confirm that the guidewire 10 is indeed moving within the location of the frontal sinus, as can be confirmed by the surgeon's knowledge of the particular anatomy of the patient being treated. In this regard, a CAT scan or other image of the sinus anatomy can be performed prior to this procedure and studied by the surgeon, to apprise the surgeon of any distinctive or unusual patterns in the individual patient's sinus anatomy which might be useful in tracking and confirmation of where the guidewire is located, as indicated by the transillumination.

Once properly positioned, the proximal end of device 10 is disconnected from connector 20, while leaving guidewire 10 in its current position. A working device 1006, for example a balloon catheter, is the introduced over guidewire 10 and advanced thereover so that the proximal end of device 10 extends proximally beyond a proximal end of device 1006. Device 10 is then reconnected to connector 20 so that light is again emitted from the light emission portion of the distal end portion of device 10 Thus it can be visually confirmed, without radiography, that the distal end portion of the guidewire 10 remains properly in the frontal sinus 1036 as the working device 1006 is advanced toward ostium 1034 and the balloon of working device 1006 is extended across the ostium, FIG. 17D. The proper positioning of the working end (distal end portion) of working device 1006 can be visualized with the scope and/or fluoroscopy.

Once proper placement of the working device 1006 has been confirmed, working device 1006 is used to perform a diagnostic or therapeutic procedure. In this particular example, the procedure is dilatation of the frontal sinus ostium 1034 by expansion of the balloon thereagainst, to enlarge the opening of the ostium 1034. However, it will be appreciated that the present invention may also be used to dilate or modify any sinus ostium or other man-made or naturally occurring anatomical opening or passageway within the nose, paranasal sinuses, nasopharynx or adjacent areas. Further, other working tools may be inserted and used according to these same techniques. After the completion of the procedure, sinus guide 1002, guidewire 10 and working device 1006 are withdrawn and removed, completing the procedure, see FIG. 17E.

Illuminating guidewire device 10 can also be used to facilitate visualization and placement of the sinus guide 1002 in the procedure described above with regard to FIGS. 17A-17E, or in another procedure in which a sinus guide, guide catheter or guide tube is placed in the sinus pathways. FIG. 18 illustrates a situation, like that described above with regard to FIG. 3, where scope 1008 has been inserted as far as possible without causing significant trauma to the patient. The range of visibility in this case does not extend all the way to ostium 1034, as indicated schematically by the rays 1009 shown extending distally from scope 1008. In this case, adequate visualization of sinus guide 1002 by scope 1008 is possible only up to the extent of the rays 1009 shown. Thus, if sinus guide 1002 is flexible enough to be advanced more closely to ostium 1034, then adequate visualization of this movement would not be possible via scope 1008. That is, if sinus guide 1002 is physically capable of being extended further distally to place the distal end thereof at the approach to ostium 1034, scope 1008 would not be capable of adequately visualizing this. However, by inserting illuminating guidewire through sinus guide 1002 as shown in FIG. 18, additional illumination can be provided distally of the illuminating range of scope 1008. This additional illumination can be received by scope 1008 to enable visualization up to the illumination portion of device 10 and potentially even extending the illumination range of device 10, as long as there is a straight pathway of the field of view. Thus, advancement of the sinus guide 1002 can be visualized further distally by the scope 1008 using this technique, and potentially all the way up to the ostium 1034.

Additionally, this technique can be used to visualize placement of the guidewire 10 up to and into the desired ostium 1034. Alternatively, this can be carried out without the sinus guide 1002, wherein the guidewire 10 is inserted and the scope 1008 can be used to visualize placement of guidewire 10 into the target ostium with the assistance of the light emitted by the scope 1008 in addition to the light emitted by guidewire 10.

In any of these procedures where a scope 1008 is used for visualization and an illuminating guidewire is inserted, some transillumination of the target sinus may occur from the light emitted by the scope 1008 alone. However, this transillumination will be diffuse and show a rather dim, large area of transillumination on the patient's skin. When the illumination guidewire is inserted and advanced, as noted earlier, a smaller, brighter transillumination spot will be visible when the illuminating portion of the guidewire has entered the sinus. Additionally, even before entering the sinus, the light emitted from the guidewire will produce a moving transillumination spot at guidewire 10 is advance, which also helps distinguish the location of the distal portion of the guidewire, relative to any diffuse transillumination produced by the scope light.

If the guidewire 10 is advanced into an ostium other than the target ostium (e.g., ostium 1035 shown in FIG. 18), this may be possible to be viewed by scope 1008, depending upon the line of sight. However, even if it is not, the transillumination resulting from entrance into a different sinus than the target sinus will be evident by the different location on the patient's face. Also, in the example shown, guidewire 10 would not be able to be advanced very far through ostium 1035 before it was diverted and curled by the relatively small sinus space that ostium 1035 leads into. Thus, by tracking the movement of the illumination spot produced by guidewire 10, the surgeon could confirm that guidewire 10 was misplaced as the guidewire would be diverted by a much smaller space then that characterized by the target frontal sinus 1036.

Thus, by using an illuminating guidewire device 10 in the methods as described above, the use of fluoroscopy or other X-ray visualization can be reduced and is not required to confirm proper placement of the guidewire in some cases.

Similar procedures may be carried out in other sinuses. For example, a similar procedure to that described above with regard to FIGS. 17A-17E may be carried out to open or expand an opening of an ostium leading to a maxillary sinus. In this case, when illuminating guidewire device 10 passes through the ostium that opens to the target maxillary sinus and enters the maxillary sinus, a relatively bright, relatively small, defined transillumination spot can be observed to move across the cheek region of the patient. As guidewire 10 is advance further distally along the maxillary sinus, the maxillary sinus typically tends to track in an inferior direction relative to the skull, and the bottom wall of the maxillary sinus is very close to the palate of the patient. Therefore as the illuminating portion of guidewire approaches and/or touches the bottom wall of the maxillary sinus, a transillumination spot can be observed on the roof of the patient's mouth by looking into the mouth of the patient. At the same time, the transillumination spot on the cheek that was caused by the guidewire will diminish, or not be visible at all at this time. This viewability on the roof of the mouth is further confirmation that the guidewire has entered the maxillary sinus. Movement of the transillumination spot on the roof of the mouth can also be observed as the guidewire 10 is advanced and/or retracted.

It is further noted that some wavelengths of light may be more effective in producing the transillumination effects described herein, for the purpose of locating the position of the guidewire. In this regard, particular wavelengths of visible light can be selected for this purpose. Alternatively, or in addition, infrared wavelengths may be particularly effective. In this regard, guidewires that employ illuminating fibers may be provided with a filter 12 to define the color/wavelength of the light emitted by device 10. As schematically shown in FIG. 19, filter 12 may be provided distally of the illumination fibers, such as at the distal tip of device 10, proximally of the illumination fibers, such as at the proximal end of device 10, or in the light pathway at a location within connector 20, for example. Multiple filters may be placed at one or more of these locations. For devices 10 that employ an LED light emitting component, different color LEDs may be employed to emit different wavelengths of light. For devices 10 that employ laser fibers, different types of lasers may be used that emit different wavelengths of light.

Another optional feature that guidewire 10 may be provided with is the ability to emit strobed, flashing or flickering light. The transillumination produced by a flashing light can be further distinguished from diffuse transillumination produced by other light sources, such as endoscopes, for example, since the transillumination produced by the guidewire 10 in this case will flicker or vary in intensity between bright and dim. To produce this type of light, either a light source having strobing capability could be connected to the device 10, or connector 20 may be provided with this capability. When using a laser light source or an LED as the light emitter, as described in embodiments above, a blinking or strobing effect can be electronically generated according to techniques known in the electronics and lighting arts. FIG. 20A schematically illustrates a connector 20 having a rotating shutter 27 rotatably mounted therein so that the vanes 27 v and gaps 27 g between the vanes (see plane view in FIG. 20B) become successively aligned with the light pathway through the connector 20 to alternate emission and blocking of light transmission out of the connector 20 and ultimately through device 10 when a device 10 is connected thereto. Shutter 27 can be powered by a motor 29 that is either battery powered or connectable to an operating room power source, and motor 29 can be operated by the user via actuator 31, which can be configured to turn the motor on and off, and optionally can be configured to vary the speed of rotation.

Alternatively, shutter 27 can be configured so that vanes 27 v extend through a slot in connector 20 whereby a user can manually rotate the shutter to cause the light emitted from device 10 to flicker.

Other instruments that are designed to be inserted into a sinus, or at least to be positioned at the ostium of a sinus can also be provided with illumination capability according to any or all of the features described above with regard to illumination guidewires. FIG. 21 shows a frontal ostium seeker 100 instrument that can be used to access a sinus ostium. For example, seeker 100 may be provided with a length of about 175 mm to about 250 mm (about 208 mm in the example shown) and a ball tip at one or both ends of the instrument. In FIG. 21, seeker 100 is also provided with a light emitter 104 at one or both ends of the device 100 that can be used to locate an end of device 100 as it is being advanced to seek an ostium, by the transillumination effects as discussed above. Light emitters 104 may be provided by LED, light illumination fibers or laser illumination fibers, for example. One or both end portions of the instrument may include a light fiber bundle or electrical wires for connection to a light source or power source in a manner as described above.

FIG. 22 shows a suction sinus instrument 110 that is configured to evacuate blood and/or other fluids from a target surgical site, such as the frontal sinus, sphenoid sinus or other sinus, to improve visibility of a surgical procedure. Instrument 110 includes an elongated shaft 116 with a distal end that opens to deliver suction via a suction lumen end 112. Additionally, a light emitter 114 is provided at the distal end of shaft 116, which may be an LED or one or more illumination fibers configured to transmit light in a manner as described above. Shaft 116 is configured and dimensioned to be inserted into the sinus passageways and sinuses. The proximal end portion of instrument 110 may include a light fiber bundle 118 or electrical wires for connection to a light source or power source in a manner as described above.

FIG. 23 shows an integrated wire dilatation catheter 120 that includes an elongate, flexible catheter shaft 126 having a balloon 128 mounted thereon. A proximal Luer hub 122 is attached to the proximal end of the catheter shaft 126. An inflation device (not shown) may be attached to the Luer hub 122 and used to inflate and deflate the balloon 128. A non-removable, integrated guide member 124 extends out of and beyond the distal end of the catheter shaft 126. Guide member 124 can extend through the length of catheter shaft 126 and extend proximally thereof as shown in FIG. 23. The proximal end portion may be configured with a polished proximal end containing illumination fibers, as described previously, or may have one or more electrical wires extending proximally thereof for connection with an electrical power source to deliver electrical power to an LED, for example. A light emitter 125 may be provided at the distal tip of integrated guide member 124, as shown in FIG. 23 and may be one or more LEDs or one or more illumination fibers, according to any of the different embodiments described above. Alternatively, light emitter 125 may be provided proximally of the distal tip of guide member 124, in a manner like that described with regard to FIG. 10, for example. Further alternatively, guide member may not extend through the entire length of catheter 126 or may not extend proximally of balloon member 128 at all. In these examples, light emitter may be an LED, wherein wires can be threaded through or alongside of catheter 126 and into guide member 124 to connect with the LED. Further alternatively, if light emitter 125 comprises one or more illumination fibers, the illumination fibers may extend proximally of the proximal end of the guide member 124, and proximally through catheter 126 where they are not surrounded by an external sheath in a guidewire formation.

In one preferred embodiment for adult applications, balloon catheter 120 has an overall length of approximately 43.5 cm and its shaft 126 has an outer diameter of about 0.058 inches. Further details about integrated wire dilatation catheters that may be configured with a light emitter in a manner as described herein can be found in co-pending application Ser. No. 11/438,090 filed May 18, 2006 and titled “Catheters with Non-Removable Guide Members Useable for Treatment of Sinusitis. Application Ser. No. 11/438,090 is hereby incorporated herein, in its entirety, by reference thereto.

Turning now to FIGS. 24-31, an illuminating guidewire 210 according to another embodiment of the present invention is depicted. Illuminating guidewire 210 may include an elongate flexible housing (or “body”), including a distal end portion 210 d and a proximal end portion 210 p. The housing (210 d and 210 p) of guidewire 210 may be coupled proximally with a connector 20, which is described further below.

Generally, distal end portion 210 d may be more flexible than proximal end portion 210 p to provide a desired degree of flexibility for leading the device to a site within a paranasal sinus or other location in the body. The distal end portion 210 d may include a coil 210 c as an exterior portion thereof, to help provide the desired flexibility to this portion. A proximal end portion 210 p of illuminating guidewire 210 provides a sufficient length so that the device extends proximally out of the patient (and, when inserted through another device, such as a sinus guide, proximally out of the device into which illuminating guidewire 210 is inserted), at all times, including the deepest contemplated location into which the distal end of device is placed. As before, the proximal end portion 210 p can have visible markings, preferably spaced at equal intervals, which can be observed by the user to confirm how far the illuminating guidewire 210 has been placed into the patient. Proximal end portion 210 p generally provides: torquability, i.e., the ability to torque the proximal end portion 210 p from a location outside of the patient and have that torque transmitted to the distal end portion 210 p; pushability, i.e., sufficient rigidity, so that when an operator pushes on the proximal end portion 210 p from a location outside of the patient, the pushing force transmits to the distal portion 210 d to advance the distal portion 210 p without buckling the device 210; and tensile strength so that an operator can pull on the proximal end portion 210 p from a location outside of the patient and withdraw the device from the patient without significant plastic deformation or any destruction of the device.

The coil 210 c formed at the distal end portion 210 d of the illuminating device 210 may be formed from a stainless steel wire. The diameter of the coil wire can be between about 0.004 and about 0.008 inches, typically about 0.006 inches. Alternative materials from which coil 210 c may be formed include, but are not limited to: ELGILOY®, CONICHROME® or other biocompatible cobalt-chromium-nickel alloys; nickel-titanium alloys; or other known biocompatible metal alloys having similar characteristics. In one approach, the coil is formed from a 0.006 inch stainless steel wire defining a 0.034 inch outer diameter (0.035 inch maximum) and a 0.021 inch inner diameter.

In one embodiment, the proximal portion 210 p can be made from a cable tube 211 (See also FIG. 26). “Cable tube,” as used in the present application, means any tubular structure other than a tube made from a single coil (such as coil 210 c). The cable tube 211 can define an approximate 0.021 inch constant inner diameter to match the inner diameter of the coil 210 c. Also, the cable tube 211 can be formed from 12-13 filars of steel wire wound to achieve maximum stiffness. A distal portion of the cable tube 211 can be tapered to provide a smooth connection to the coil 210 c. This tapered profile can be formed by grinding an exterior of the cable tube 211. In one embodiment, proximal portion 210 p, made of cable tube 211, may provide significantly more torquability and pushability than distal end portion 210 d, made of coil 210 c. Conversely, distal end portion 210 d may be more flexible than proximal portion 210 p. As shown in FIG. 25, coil 210 c is joined to proximal portion 210 p by solder, epoxy or other adhesive or mechanical joint. In one approach, coil 210 c has a length in the range of 5-8 cm and the cable tube (i.e., proximal portion 210 p) is 60-100 cm in length. One or more illumination channels for an illumination fiber 210 i are provided in guidewire 210 and extend the length thereof. The illumination channels are configured to transport light from the proximal end of illumination guidewire 210 to and out of the distal end of device. One or more illumination channels can be provided, each comprising a plastic illumination fiber. As previously described, the plastic used to make the illumination fibers is compounded for light transmission properties according to techniques known and available in the art. Accordingly, ESKA™ (Mitsubishi Rayon), a high performance plastic optical fiber may be used, which has a concentric double-layer structure with high-purity polymethyl methacrylate (PMMA) core and a thin layer of specially selected transparent fluorine polymer cladding. In a preferred approach, the assembly includes two illumination fibers each having an outside diameter of about 0.010″. It is to be noted, however, that the illumination fibers can have an outside diameter in the range of about 0.005 inches to about 0.010 inches. Alternatively, a single plastic illumination fiber may be used that has an outside diameter of about 0.020″. Moreover, glass illumination fibers may be substituted which are much smaller in outside diameter, e.g., about 0.002″. In this case, more illumination fibers may be provided in a bundle, e.g., about six to fifty glass fibers may be provided.

The distal end of the illumination guidewire 210 is sealed by a transparent (or translucent) seal 210 s which may be in the form of epoxy or other transparent or translucent adhesive or sealing material. The seal 210 s maintains the distal ends of illumination fibers 210 i coincident with the distal end of the device and provides a lens 213 to provide an atraumatic tip. In one approach, an UV adhesive is employed to bond the illumination fibers 210 i to the coiled wire 210 c as well as to a core wire. Further, the seal 210 s prevents entrance of foreign materials into the device. The lens 213 formed at the distal end can be designed to either focus or distribute the light as it emanates therefrom, to achieve maximum transillumination effects. Moreover, the distal end can also include a prism or diffracting element.

Still referring to FIG. 25, in some embodiments, guidewire 210 may further include an inner core wire 210 cw (or “core wire”). In one embodiment, as shown in FIG. 25, core wire 210 cw may extend from the distal end of distal portion 210 d to the proximal end of proximal portion 210 p of guidewire 210 and may be attached to coil 210 c and cable tube 211 at the distal end, at a junction between coil 210 c and cable tube 211, and at a proximal end. In various embodiments, core wire 210 cw may be attached by any suitable means, such as by laser welding, epoxy or other adhesive or mechanical fixture. In one embodiment, core wire 210 cw may be formed from NITINOL (nickel-titanium alloy) metal alloys that are biocompatible and provide the necessary rigidity and torquability.

Core wire 210 cw particularly increases the pushability and the torquability of coil 210 c which, by itself, is quite flexible and twistable. Combined with the core wire 210 cw, distal portion 210 d is much more effective at transferring pushing and torquing forces without buckling or twisting. Additionally, core wire 210 cw may be plastically deformed or memory set into a bent shape, an example of which is shown in FIG. 5. Bend 10 b provides a steerability function, allowing an operator to direct the distal end of device 10 in different directions by torquing the device about the longitudinal axis of the device, as indicated by the arrows in FIG. 5.

As shown in FIGS. 27 and 28, core wire 210 cw may be formed as an elongate member. When so formed, core wire 210 cw may be ground to different diameters to provide varying amounts of rigidity and torquability along illumination guidewire 210. As part of an illuminating guidewire 210 assembly, core wire 210 cw is configured to provide a space for the light fibers 210 i. Thus, the major dimension of the core wire 210 cw must be less than an inner diameter of the proximal portion 210 p.

With reference to FIG. 27, in one embodiment, core wire 210 cw may include a distal end portion 219 having a nominal diameter of 0.003 inches and a length of approximately 1.0 centimeters. A proximally adjacent section 221 can have a diameter of approximately 0.006 inches and a length extending about 4.0 centimeters from the terminal end of the member. A tapered region 223 is configured proximally of this structure, increasing in size to a nominal diameter of about 0.008 inches approximately 7 centimeters from the terminal end. The remaining proximally oriented section 225 of core wire 210 cw can embody a constant 0.008 inch diameter. In this way, the various dimensional sections of core wire 210 cw can provide desirable flexibility.

In an alternative embodiment, referring now to FIG. 28, core wire 210 cw may include structures which accommodate a transition from coil 210 c to proximal portion 210 p. A short terminal end portion 231 of this embodiment (approximately 0.2 cm in length), is flattened for attachment (such as soldering) purposes. The support 210 cw then forms a 0.005 inch diameter 233 for approximately 1.3 cm and from about 1.5 cm to 5.0 cm from the terminal end, the support 210 cw has a tapered profile 235 increasing to a maximum diameter of about 0.008 inches. Between approximately 5.0 cm and 8.0 cm from the terminal end, core wire 210 cw includes a distal enlarged section with a proximally oriented taper section 237 that assumes the diameter of about 0.008 inches then tapers down to about 0.006 inches in a proximally oriented section 239. This section 239 then increases in diameter to a maximum of approximately 0.008 inches at about 12.0 cm for the terminal end. The section 241 proximal to this maintains a diameter of about 0.008 inches.

Turning now to FIG. 29, core wire 210 cw can be fixed within an illuminating guidewire 210 by attaching a terminal end 251 of the support 210 cw to the coil 210 c. At a junction 253 between the proximal the proximal portion 210 p of the device 210 and the coil 210 c, the proximal taper of the distal enlarged section 238 of core wire 210 cw can be configured. This juxtapositional relationship of core wire 210 cw and the coil 210 c and proximal portion 210 p facilitates easing stiffness in the region at the junction 253.

In an alternate embodiment, as shown in FIG. 30, the 0.006 inch section 239 of core wire 210 cw can be configured and welded or otherwise attached to the junction 253 between the proximal portion 210 p and coil 210 c, as well as at the terminal end 251. It is to be recognized that a weld at the junction 253 may require additional material (i.e., steel ring) to complete a bond between the pieces. If a soldering approach is used, the inner diameter of the coil can be kept open by inserting a Teflon coated mandrel to fill the inner diameter. In this way, the torque between the proximal portion 210 p and the distal end of the illuminating guidewire 210 can be substantially enhanced through torque transfer because there is a relatively shorter length of core wire 210 cw to transfer a rotation force. This approach can also involve removing a connection between the proximal portion 210 p and core wire 210 cw at a proximal end of core wire 210 cw.

With reference to FIG. 31, another embodiment of an illuminating guidewire 210 is depicted. Here, core wire 210 cw is attached at its distal end 251 to a coil 210 c and is also attached along a midsection at the junction 253 between the proximal portion 210 p of illuminating guidewire 210 and coil 210 c. Core wire 210 cw can also have a length substantially less than that of the illuminating device 210. Thus configured, core wire 210 cw can have a terminal point 261 which terminates along a midsection of the illuminating guidewire 210. The space unoccupied by core wire 210 cw provides an area for light fibers 210 i to move. In one embodiment, a 40-60 cm section can be provided for the winding up of the fibers 210 i distal to a connector assembly 20. This can help to prevent damage to the fibers 210 i during rotation of the illuminating guidewire 210.

It has been observed that the illuminating fibers 210 i can be subjected to thermal cycling. This is due to sterilization, aging, shipping, illumination of the fibers, and other factors. Such thermal cycling can result in longitudinal shrinkage of the illuminating fibers 210 i. In fact, shrinkage of from 0.5 to 1% can occur when illuminating fibers are heated above 40° C. In conventional approaches, illuminating fiber shrinkage can result in damage where the fibers are anchored in a manner which does not compensate for shrinkage. Ends of the fibers can become shredded or frayed which thereby adversely affects the functioning of the fibers. Various approaches are contemplated to address shrinkage of illuminating fibers. In one approach, a fiber can be pre-heat treated at approximately 70° C. for 48 hours. By doing so, the fiber can be pre-shrunk. This can minimize or eliminate further shrinkage at lower temperatures.

In other approaches, referring now to FIGS. 31 and 32, structures can be incorporated into the illuminating guidewire assembly 210 to accommodate changes in length. As previously stated, a connector 20 is attached at a proximal end of illuminating guidewire 210. Connector 20 can in turn be operatively associated with a power source or other light activation system. As shown in FIGS. 32 and 33, a first embodiment of a connector 220 incorporating structures that accommodate light fiber length changes includes a luer connector 224 that receives a cable tube 226 of a proximal end portion 210 p of an illuminating guidewire 210.

The connector 220 further includes an internal bore 227 having first 229, second 232, and third 234 sections, the first 229 and third 234 having generally equal diameter and the second section 232 having a diameter less than first 229 and third 234. The first bore section 229 is formed at a front end of the connector 220 and is diametrically sized to receive a centering sleeve 236. The sleeve 236 includes a bore sized to accept the cable tube 226 and functions to center the cable tube 236 within the first section 229.

The third bore section 234 of the connector 220 extends distally from a proximal end of the connector 220. Received at a back end of the third bore section 229 is a centering grommet 240 which attachingly engages the illuminating fibers 210 i. The grommet 240 centers the light fiber 210 i through a connection point 242.

Further, attached to a proximal portion of the cable tube 226 is a collet 244. The collet 244 is sized and shaped to slide within the third bore section 234 which has a length substantially larger than a length of the collet. Through its smaller diameter when compared to the adjacently arranged first and third bore sections 229, 234, the second bore section 232 acts as a stop for both the distally arranged centering sleeve 236 and the proximally positioned collet 244.

As stated, a proximal end of the illuminating fiber 210 i is attached to the centering grommet. Its distal end is bonded to a distal end of guidewire 210 The cable tube 226, however, has a floating proximal end by way of its connection to slidable collet 244. Should the illuminating fiber 210 i shrink in length, such length shrinkage is taken up by collet 241 (and cable tube 226, which is connected to collet 244) moving proximally within the third bore section 234 of the connector 220. In this way, structural damage to the shorter length illuminating fiber 210 i is avoided.

Referring now to FIG. 34, in an alternate embodiment of connector 220, the centering sleeve (236 in the embodiment of FIG. 33) may be omitted. Turning now to FIGS. 35 and 36, yet another alternative approach is shown. A proximal end of the illuminating fiber 210 i is affixed to a light fiber connector 243 configured in a proximal end of an internal bore 245 extending through the connector 220. In this embodiment, the internal bore includes a first larger diameter section which tapers down to a second smaller, constant diameter bore section. The illuminating fiber 210 i is received in a third bore section 243 which has a diameter smaller than the first and second sections.

Additionally, slidably configured within the first bore section is a rigid grommet 247 including a first component of a rotational stop 249. Also disposed in the first bore section is a second component of a rotational stop 252 formed therein. The grommet 247 is thus keyed with the connector 220 to control the degree to which the components can rotate with respect to each other. In one approach, rotation can be limited to 220 degrees or to 150 degrees where two rotational stops 249 and 252 are configured within the connector 220. A cap 253 retains the grommet 247 within the connector bore 245. As so configured, the cap 253 prevents the grommet 247 from moving in response to a tension applied on the illuminating guidewire 210 Additionally, the bore 245 permits longitudinal translation of the cable tube which is attached to the grommet 247. Moreover, as stated, the keyed grommet relationship of the connector 220 controls the permissible rotation of the cable tube 226 and thus the fiber 210 i. Accordingly, the illuminating fiber 210 i is protected should it tend to shrink as well as when tension and rotational forces are placed on the device.

Turning now to FIGS. 37-38 inclusive, an illuminating guidewire 310 according to another embodiment of the present invention is depicted. Illuminating guidewire 310 may include an elongate flexible housing (or “body”), including a distal end portion 310 d and a proximal end portion 310 p.

Generally, distal end portion 310 d may be more flexible than proximal end portion 310 p to provide a desired degree of flexibility for leading the device to a site within a paranasal sinus or other location in the body. The distal end portion 310 d may include a coil 310 c as an exterior portion thereof, to help provide the desired flexibility to this portion. A proximal end portion 310 p of illuminating guidewire 310 provides a sufficient length so that the device extends proximally out of the patient (and, when inserted through another device, such as a sinus guide, proximally out of the device into which illuminating guidewire 310 is inserted), at all times, including the deepest contemplated location into which the distal end of device is placed. As before, the proximal end portion 310 p can have visible markings, preferably spaced at equal intervals, which can be observed by the user to confirm how far the illuminating guidewire 310 has been placed into the patient. Proximal end portion 310 p generally provides: torquability, i.e., the ability to torque the proximal end portion 310 p from a location outside of the patient and have that torque transmitted to the distal end portion 310 d; pushability, i.e., sufficient rigidity, so that when an operator pushes on the proximal end portion 310 p from a location outside of the patient, the pushing force transmits to the distal portion 310 d to advance the distal portion 310 d without buckling the device 310; and tensile strength so that an operator can pull on the proximal end portion 310 p from a location outside of the patient and withdraw device from the patient without significant plastic deformation or any destruction of the device.

Again referring to FIG. 37, coil 310 c forms the distal end portion 310 d of illuminating device 310 and may be formed from a stainless steel wire. The diameter of the coil wire can be between about 0.004 and about 0.008 inches, typically about 0.006 inches. Alternative materials from which coil 310 c may be formed include, but are not limited to: ELGILOY®, CONICHROME® or other biocompatible cobalt-chromium-nickel alloy; nickel-titanium alloys; or other known biocompatible metal alloys having similar characteristics. In one approach, the coil is formed from a 0.006 inch stainless steel wire defining a 0.034 inch outer diameter (0.035 inch maximum) and a 0.021 inch inner diameter.

In one embodiment, the proximal portion 310 p can be made from a cable tube 311. “Cable tube,” as used in the present application, means any tubular structure other than a tube made from a single coil (such as coil 310 c). The cable tube 311 can define an approximate 0.021 inch constant inner diameter to match the inner diameter of the coil 310 c. Also, cable tube 311 can be formed from 5-20 filars of steel wire wound together with 12-13 filars selected to achieve a preferred stiffness. A distal portion of the cable tube 311 can be tapered to provide a smoother connection to the coil 310 c. This tapered profile can be formed by grinding an exterior of cable tube 311. In one embodiment, proximal portion 310 p, made of cable tube 311, may provide significantly more torquability and pushability than distal end portion 310 d, made of coil 310 c. Conversely, distal end portion 310 d may be more flexible than proximal portion 310 p.

In some embodiments, coil 310 c has a length in the range of 5-15 cm and the cable tube (i.e., proximal portion 310 p) is 60-100 cm in length. One or more illumination channels for an illumination fiber 310 i are provided in guidewire 310 and extend the length thereof. The illumination channels are configured to transport light from the proximal end of illumination guidewire 310 to and out of the distal end of device. One or more illumination channels can be provided, each comprising a plastic illumination fiber. As previously described, the plastic used to make the illumination fibers is compounded for light transmission properties according to techniques known and available in the art. Accordingly, ESKA™ (Mitsubishi Rayon), a high performance plastic optical fiber may be used, which has a concentric double-layer structure with high-purity polymethyl methacrylate (PMMA) core and a thin layer of specially selected transparent fluorine polymer cladding. In a preferred approach, the assembly includes two illumination fibers each having an outside diameter of about 0.010″. It is to be noted, however, that the illumination fibers can have an outside diameter in the range of about 0.005 inches to about 0.010 inches. Alternatively, a single plastic illumination fiber may be used that has an outside diameter of about 0.020″. Moreover, glass illumination fibers may be substituted which are much smaller in outside diameter, e.g., about 0.002″. In this case, more illumination fibers may be provided in a bundle, e.g., about six to fifty glass fibers may be provided.

In some embodiments, guidewire 310 may further include an inner core wire 310 cw (or “core wire”) in certain sections and may extend from the distal end of distal portion 310 d to the proximal end of proximal portion 310 p of guidewire 310 and may be attached to coil 310 c and cable tube 311 at the distal end, at a junctions between coil 310 c and cable tube 311, and at a proximal end. In various embodiments, core wire 310 cw may be attached by any suitable means, such as by laser welding, epoxy or other adhesive or mechanical fixture. In one embodiment, core wire 310 c w may be formed from NITINOL (nickel-titanium alloy) metal alloys that are biocompatible and provide the necessary rigidity and torquability. In a preferred embodiment discussed hereinafter, core wire 310 cw terminates at a point approximately midway through device 310 with a fixed distal end and a floating (i.e., not fixed or bonded) proximal end. As noted in the ensuing description, core wire 310 cw may be bonded at various other points along device 310 such as those identified as 301 sj 1, 301 sj 1 and 301 sj 3.

Core wire 310 cw particularly increases the pushability and the torquability of coil 310 c which, by itself, is quite flexible and twistable. Combined with the core wire 310 cw, distal portion 310 d is much more effective at transferring pushing and torquing forces without buckling or twisting. Additionally, core wire 310 cw may be plastically deformed or memory set into a bent shape allowing an operator to direct the distal end of device 310 in different directions by torquing device about the longitudinal axis of the device.

Analogous to FIGS. 27 and 28, core wire 310 cw may be formed as an elongate member. When so formed, core wire 310 cw may be ground to different diameters to provide varying amounts of rigidity and torquability along illumination guidewire 310. As part of an illuminating guidewire 310 assembly, core wire 310 cw is configured to provide a space for the illumination fibers 310 i. Thus, the major dimension of the core wire 310 cw must be less than an inner diameter of the proximal portion 310 p.

More particularly, FIGS. 37A-A through 37F-F illustrate axial cross sectional views of guidewire 310 along various points along the length of the device and describe components contained within the various points of guidewire 310.

As shown in FIG. 37A-A, which represents the distal coil region of guidewire 310, illumination fibers 310 i and core wire 310 cw are housed within coil 310 c. As a note and again referring to FIG. 37, the distal end of the illumination guidewire 310 is sealed by a transparent (or translucent) seal 310 s which may be in the form of epoxy or other transparent or translucent adhesive or sealing material. The seal 310 s maintains the distal ends of illumination fibers 310 i coincident with the distal end of the device and provides a lens 313 to provide an atraumatic tip. In one approach, an UV adhesive is employed to bond the illumination fibers 310 i to coil 310 c as well as to a core wire 310 cw. Further, the seal 310 s prevents entrance of foreign materials into the device. The lens 313 formed at the distal end can be designed to either focus or distribute the light as it emanates therefrom, to achieve maximum transillumination effects. Moreover, the distal end may also include a prism or diffracting element. Additionally 310 sj 1 represents a soldering joint where the same types of soldering materials previously describes herein are suitable for use for 310 sj 1. The joining of core wire 310 cw with coil 310 c may be made by epoxy (or other adhesive), by mechanical joint, or laser welding.

Referring to FIG. 37B-B and FIG. 37C-C which represent regions of illuminated guidewire 310 which include the transition zone from the coil 310 c to cable tube 311, one sees stranded wire 310 sw. As will be seen in the discussion of the ensuing figures, stranded wire 310 sw functions to provide stress relief within the system and absorb loads that would otherwise be transferred to the more delicate illumination fibers 310 i. Stranded wire 310 sw may be made of any flexible, medically safe material that can be braided together yet provide sufficient strength in tension to withstand abrupt pulling or jerking Such materials include stainless steel and nitinol.

In a preferred embodiment, the stranded wire 310 sw has an overall diameter of approximately 0.005 inches. By varying the number and thickness of the strands comprising stranded wire 310 sw, flexibility and ability to wind (twist) illuminating guidewire 310 is achieved. In most preferred embodiments, seven strands of stainless steel having a diameter of approximately 0.002 inches or 19 strands of stainless steel having approximately a diameter of approximately 0.001 inches, provide satisfactory strength and flexibility to withstand abrupt jerking or pulling and the ability to twist during use.

FIG. 37D-D represents a portion of illuminating device 310 near the proximal end of the device. In this view, core wire 310 cw is no longer present since in this embodiment it terminates at a location before reaching the proximal end of the device. The termination point is analogous to terminal point 261 of the previously described embodiment shown in FIG. 31.

FIG. 37E-E and FIG. 37F-F illustrate another region of transition in the proximal region of illuminating device 310. Particularly, cable tube 311 is shown to be within floating tube 310 ft. of FIG. 37E-E which then transitions to no cable tube 311 being present in FIG. 37 F-F and bonding tube 310 bt is present as shown in FIG. 37F-F.

Floating tube 310 ft functions to provide a surface where illuminating guidewire 310 is grasped or otherwise engaged by a locking or securing mechanism of a light connector. Floating tube 310 ft is fixably bonded at its proximal end (as described in FIG. 38C) but allowed to “float” at its distal end (i.e., not fixably bonded to cable tube 311, as described in FIG. 38B). Floating tube 310 ft thus permits stranded wire 310 sw and illumination fibers 310 i to twist within illuminating device 310. The ability of stranded wire 310 sw and illumination fibers 310 i to twist is quite advantageous as the device in use will typically be turned as it is advanced in the oftentimes tortuous bodily cavities such as those present in the paranasal sinuses.

Floating tube 310 ft may be made of any suitable, medically safe material that imparts sufficient rigidity and strength to house the various internal elements of illuminating guidewire 310 and sustain engagement by a light connector. Examples of such materials are those used to manufacture hypotubes for medical applications and include stainless steel, titanium, elgiloy, and PEEK tubing.

Bonding tube 310 bt functions to fixably bond all of illuminating guidewire 310's elements that are present at the proximal end of the device as explained in the discussion of FIG. 38C.

Bonding tube 310 bt may be any suitable, medically safe material that imparts sufficient rigidity and strength to house the various internal elements of illuminating guidewire 310 and provide a surface for bonding materials (such as epoxy or other medically safe adhesives) to join the internal elements in the proximal end of the device. Examples of such medically safe materials including block copolymers such as those sold under the tradename PEBAX, nylon, polycarbonates, polyimides and other plastics such as acrylonitrile-butadiene-styrene copolymer (ABS).

FIG. 38 provides an overall view where major transitions occur along the length of illuminating device 310 FIG. 38A, FIG. 38B and FIG. 38C show the details for specific zones or regions of the device.

Referring to FIG. 38A, the transitional between coil 310 c and cable tube 311 is shown. In this embodiment, illumination fibers 310 i pass through this region. Cable tube 311 is bonded to coil 310 c, stranded wire 310 sw and core wire 310 cw by solder joint 310 sj 3. In addition, solder joint 310 sj 2 joins coil 310 c, stranded wire 310 sw and core wire 310 cw. The significance of having these two bonding points not only has been demonstrated to insure a smooth transition between cable tube 311 and coil 310 c but enhances the bendability across this region by forming a near natural bending curve, i.e., one without any severe kinking. Desirably the distance between solder joint 310 sj 2 and solder joint 310 sj 3 ranges from 0.020 to 0.060 inches. It has been found that if the distance between solder joint 310 sj 2 and solder joint 310 sj 3 is less than 0.020 inches, this section becomes too stiff and possesses less of a natural bend when flexed. If the distance is greater than 0.060 inches, the region becomes too flexible and not stiff enough to advance the guidewire without kinking. Generally, bending of this region without severe kinking have been determined to range from a distance about ½ to 4 times the outside diameter of the housing portions to be joined, more preferably no more than 3 times the outside diameter of the housing portions to be joined.

FIG. 38B illustrates the transition between cable tube 311 and floating tube 310 ft. Of particular importance in this view is that cable tube 311 (and hence its contents, i.e., illumination fibers 310 i and stranded wire 310 sw ) are not fixably bonded to floating tube 310 ft. Therefore, cable tube 311 and its contents are free to rotate with respect to floating tube 310 ft which is a desirable feature when navigating the tortuous cavities of the paranasal sinuses.

Finally, FIG. 38C shows the configuration of the proximal end of illumination device 310 In this figure, proximal end of illumination guidewire 310 is sealed by a transparent (or translucent) seal 310 s (similar to the one on the distal end) which may be in the form of epoxy or other transparent or translucent adhesive or sealing material. The seal 310 s maintains the proximal ends of illumination fibers 310 i coincident with the proximal end of the device and provides a lens 310 pl to provide an atraumatic tip. In one approach, an UV adhesive is employed and applied into adhesive region 310 ad 1 to bond illumination fibers 310 i, bonding tube 310 bt as well as to bond stranded wire 310 sw to seal 310 s. Further, the seal 310 s prevents entrance of foreign materials into the device. The lens 310 pl formed at the proximal end can be designed to either focus or distribute the light as it enters from a light cable or other light source, to achieve maximum transillumination effects. FIG. 38C also shows the proximal end of floating tube 310 ft which is fixably bonded to bonding tube 310 bt. While any suitable bonding method may be used to bond floating tube 310 ft to bonding tube 310 bt, use of a medically safe adhesive is preferred and provided to adhesion region 310 ad 2 and in fact may be bonded at the same time and with the bonding materials used in adhesion region 310 ad 1.

It has been observed that illumination connectors, i.e., devices that join an illumination guidewire device to a light cable of a light source, are prone to heating which could be detrimental to components of an illuminated guidewire as well as to the illumination device's effectiveness to provide adequate lighting at the distal end. In some instance temperatures of greater than 250° F. have been observed. The illumination connector hereinafter described helps to better control heat buildup.

FIG. 39 represents illumination connector 320 comprising body 322, button 330 and button springs 332. Body 332 overall comprises conical distal bore 328, center bore 326, light cable connection receiver 324. Button 330 further comprises bore 334. In use, connector 320 receives illumination guidewire 310 through distal bore 328. While depressing button 330 downwardly and further advancing illumination guidewire 310 through button bore 334 until it reaches proximal aperture 340. Illumination guidewire 310 is secured in connector 320 once button 330 is released and springs 332 move button bore 334 to secure floating tube 310 ft as button bore 334 is urged from axial alignment with center bore 326. As noted earlier, with floating tube 310 ft being the section of illumination device 310 that is secured within connector 320, cable tube 311 and its contents are able to rotate.

FIG. 39A contains further detail of the proximal end of connector 320. In particular, illumination device 310 rests in aperture 340. It is significant that the diameter of aperture 340 is less than the diameter of the proximal end of illuminated device 310 It has been determined that aperture outer diameters that range from about 60 to 80% (preferably about 70%) of the outer diameter of the proximal end of the illumination device provide satisfactory light dissipation while maintaining sufficient light transmission through the illumination fibers to the distal end of the device. Further noteworthy features of connector 320 are that proximal lens 310 pl does not protrude out of aperture 340 (so as not to come into direct contact with a light source) and that there is slope 342 inside center bore 326. These features further help to maintain reliable operation of the illuminated guidewire by dissipating errant light transmitted through light cables of powerful light sources preventing the excess light from turning to heat. These features also allow for consistent light output from light sources that produce a low amount of light.

It should be noted that having body 320 made of a translucent material aids in errant light dissipation. Preferably, body 320 is made of a translucent material that has a translucency of greater or equal to 70%. These levels of translucency are easily obtained with medically safe plastics and may be adjusted incorporating varying levels of dye to achieve a desired translucency.

It has been observed that the illuminating fibers 310 i can be subjected to thermal cycling. This is due to sterilization, aging, shipping, illumination of the fibers, and other factors. Such thermal cycling can result in longitudinal shrinkage of the illuminating fibers 310 i. In fact, shrinkage of from 0.5 to 1% can occur when illuminating fibers are heated above 40° C. In conventional approaches, illuminating fiber shrinkage can result in damage where the fibers are anchored in a manner which does not compensate for shrinkage. Ends of the fibers can become shredded or frayed which thereby adversely affects the functioning of the fibers.

Various approaches are contemplated to address shrinkage of illuminating fibers. In one approach, a fiber can be pre-heat treated at approximately 70° C. for 48 hours. By doing so, the fiber can be pre-shrunk. This can minimize or eliminate further shrinkage at lower temperatures.

In still other contemplated approaches to compensate for changes in illuminating fiber length, the core wire can be alternatively or additionally collapsible and include such structure as a spring or corrugated section. The core wire can also be severed in places to accommodate length changes.

The disclosed illuminating guidewire assembly can be used in a myriad of applications. In addition to use in the sinuses, the assembly can be employed in vascular applications such as by providing a way to map or help diagnose anatomy while it is advanced therethrough. Also, the device can be useful in illuminating deep tissue or can be used in the gastrointestinal track for similar purposes.

Moreover, while the present invention has been described with reference to the specific embodiments thereof, various changes may be made and equivalents may be substituted without departing from the true spirit and scope of the invention. In addition, many modifications may be made to adapt a particular situation, material, composition of matter, process, process step or steps, to the objective, spirit and scope of the present invention. All such modifications are intended to be within the scope of the claims appended hereto. 

What is claimed:
 1. A proximal assembly of an illuminating guidewire comprising: a first tube having a lumen extending therethrough; an elongate flexible housing having a lumen extending therethrough, the housing being received within the first tube but not extending proximally beyond the proximal end of the first tube; a second tube having a lumen therethrough and positioned within the lumen of the first tube at the proximal end and extending beyond the proximal end of the first tube, but not beyond the distal end of the first tube; at least one illuminating fiber extending through and proximally beyond the lumen of the housing and the lumen of the first tube and into the lumen of the second tube; and wherein the housing is not fixably attached to the first tube and is free to rotate within the first tube and the distal end of the second tube and the proximal end of the first tube are fixably attached.
 2. The assembly of claim 1, wherein the housing is a cable tube.
 3. The assembly of claim 2, wherein the first tube is a hypotube.
 4. The assembly of claim 3, wherein the second tube is made of a block copolymer resin.
 5. The assembly of claim 4 further comprising a stranded wire extending through and proximally beyond the lumen of the housing and the lumen of the first tube and into the lumen of the second tube.
 6. The assembly of claim 5 further comprising an adhesive lens which is fixable attached to the proximal end of the second tube and is fixably attached to the at least one illuminating fiber.
 7. The assembly of claim 6 wherein the at least one illuminating fiber comprises at least two illuminating fibers. 